High frequency array ultrasound system

ABSTRACT

A system for acquiring an ultrasound signal comprises a signal processing unit adapted for acquiring a received ultrasound signal from an ultrasound transducer having a plurality of elements. The system is adapted to receive ultrasound signals having a frequency of at least 20 megahertz (MHz) with a transducer having a field of view of at least 5.0 millimeters (mm) at a frame rate of at least 20 frames per second (fps). The signal processing can further produce an ultrasound image from the acquired ultrasound signal. The transducer can be a linear array transducer, a phased array transducer, a two-dimensional (2-D) array transducer, or a curved array transducer.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. Provisional PatentApplication No. 60/733,091 filed Nov. 2, 2005, and the benefit of U.S.Provisional Patent application No. 60/733,089 filed Nov. 2, 2005, bothof which are fully incorporated herein and made a part hereof.

BACKGROUND OF THE INVENTION

Ultrasound echography systems using an arrayed transducer have been usedin human clinical applications where the desired image resolution is inthe order of millimeters. Operating frequencies in these clinicalsystems are typically below 10 MHz. With these low operatingfrequencies, however, such systems are not appropriate for imaging wherehigher resolutions are needed, for example in imaging small animals suchas mice or small tissue structures in humans.

Moreover, small animal imaging applications present several challengingrequirements which are not met by currently available imaging systems.The heart rate of an adult mouse may be as high as 500 beats per minute,so high frame rate capability may be desired. The width of the regionbeing imaged, the field of view, should also be sufficient to includethe entire organ being studied.

Ultrasound systems for imaging at frequencies above 15 MHz have beendeveloped using a single element transducer. However, arrayedtransducers offer better image quality, can achieve higher acquisitionframe rates and offer other advantages over single element transducersystems. The embodiments according to the present invention overcomemany of the challenges in the current art, including those describedabove.

SUMMARY OF THE INVENTION

Provided herein is a system and method for acquiring an ultrasoundsignal comprised of a signal processing unit adapted for acquiring areceived ultrasound signal from a ultrasound transducer having aplurality of elements. The system can be adapted to receive ultrasoundsignals having a frequency of at least 15 megahertz (MHz) with a fixedtransducer having a field of view of at least 5.0 millimeters (mm) at afrane rate of at least 20 frames per second (fps). The signal processingunit can further produce an ultrasound image from the acquiredultrasound signal. The transducer can be, but is not limited to, alinear array transducer, a phased array transducer, a two-dimensional(2-D) array transducer, or a curved array transducer. The system caninclude such a transducer or be adapted to operate with such atransducer.

Also provided herein is a system and method for acquiring an ultrasoundsignal comprising a processing unit for acquiring received ultrasoundsignals from an ultrasound transducer operating at a transmit andreceive frequency of at least 15 MHz, wherein the processing unitcomprises a signal sampler that uses quadrature sampling to acquire theultrasound signal.

Additional advantages of the invention will be set forth in part in thedescription which follows, and in part will be obvious from thedescription, or may be learned by practice of the invention. Theadvantages of the invention will be realized and attained by means ofthe elements and combinations particularly pointed out in the appendedclaims. It is to be understood that both the foregoing generaldescription and the following detailed description are exemplary andexplanatory only and are not restrictive of the invention, as claimed.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of this specification, illustrate several embodiments according tothe invention and together with the description, serve to explain theprinciples of the invention:

FIG. 1 is a representation in block diagram form of a computingoperating environment;

FIGS. 2A-2C, are exemplary top, bottom and cross-sectional views of anexemplary schematic PZT stack of the present invention, the top viewshowing, at the top and bottom of the PZT stack, portions of the groundelectric layer extending outwardly from the overlying lens; the bottomview showing, at the longitudinally extending edges, exposed portions ofthe dielectric layer between individual signal electrode elements (asone will appreciate, not show in the center portion of the PZT stack arethe lines showing the individualized signal electrode elements—onesignal electrode per element of the PZT stack);

FIG. 3A is a top plan view of an interposer for use with the PZT stackof FIGS. 2A-2C, showing electrical traces extending outwardly fromadjacent the central opening of the transducer and ground electricaltraces located at the top and bottom portions of the interposer, showinga dielectric layer disposed thereon a portion of the surface of theinterposer, the dielectric layer defining an array of staggered wellspositioned along an axis parallel to the longitudinal axis of theinterposer, each well communicating with an electrical trace of theinterposer, and further showing a solder paste ball bump mounted thereineach well in the dielectric layer such that, when a PZT stack is mountedthereon the dielectric layer and heat is applied, the solder melts toform the desired electrical continuity between the individual elementsignal electrodes and the individual trances on the interposer—the wellhelping to retain the solder within the confines of the well;

FIG. 3B is a partial enlarged view of the staggered wells of thedielectric layer and the electrical traces of the underlying interposerof FIG. 3A, the well sized to accept the solder paste ball bumps;

FIG. 4A is a top plan view of the PZT stack of FIG. 2A mounted thereonthe dielectric layer and the interposer of FIG. 3A;

FIG. 4B is a top plan view of the PZT stack of FIG. 2A mounted thereonthe dielectric layer and interposer of FIG. 3A, showing the PZT stack asa transparent layer to illustrate the mounting relationship between thePZT stack and the underlying interposer, the solder paste ball bumpsmounted therebetween forming an electrical connection between therespective element signal electrodes and the electrical traces on theinterposer;

FIG. 5A is a schematic top plan view of an exemplary circuit board formounting the transducer of the present invention thereto, the circuitboard having a plurality of board electrical traces formed thereon, eachboard electrical trace having a proximal end adapted to couple to anelectrical trace of the transducer and a distal end adapted to couple toa connector, such as, for example, a cable for communication of signalstherethrough;

FIG. 5B is a top plan view of an exemplary circuit board for mounting ofan exemplary 256-element array having a 75 micron pitch;

FIG. 5C is a top plan view of the vias of the circuit board of FIG. 5Bthat are in communication with an underlying ground layer of the circuitboard;

FIG. 6 is a top plan view of a portion of the exemplified circuit boardshowing, in Region A, the ground electrode layer of the transducer wirebonded to an electrical trace on the interposer, which is, in turn, wirebonded to ground pads of the circuit board, and further showing, inRegion B, the individual electrical traces of the transducer wire bondedto individual board electrical traces of the circuit board;

FIG. 7A is a partial enlarged cross-sectional view of Region A of FIG.6, showing the dielectric layer positioned about the solder paste ballbumps and between the PZT stack and the interposer;

FIG. 7B is a partial enlarged cross-sectional view of Region B of FIG.6, showing the dielectric layer between the PZT stack and theinterposer;

FIGS. 8A and 8B are partial cross-sectional views of an exemplifiedtransducer mounted to a portion of the circuit board;

FIG. 9 is an enlarged partial view Region B of an exemplified transducermounted to a portion of the circuit board;

FIG. 10 is a partial enlarged cross-sectional view of a transducer thatdoes not include an interposer, showing a solder paste ball bump mountedthereon the underlying circuit board, each ball bump being mounted ontoone board electrical trace of the circuit board, and showing the PZTstack being mounted thereon so that the respective element signalelectrodes of the PZT stack are in electrical continuity, via therespective ball bumps, to their respective board electrical trace of thecircuit board;

FIG. 11A is a partial enlarged cross-sectional view of FIG. 10, showingthe ground electrode layer of the transducer without an interposer wirebonded to ground pads of the circuit board;

FIG. 11B is a partial enlarged cross-sectional view of FIG. 10, showingthe ball bump disposed therebetween and in electrical communication withthe electrical trace of the circuit board and the element signalelectrode of the PZT stack;

FIG. 12A is a schematic showing the flex circuit board and a pair ofSamtec BTH-090 connectors mounted to a rigid portion of the circuitboard;

FIG. 12B is an exemplary pin-out table for the connector shown in FIGS.5B and 12A;

FIG. 13 is a schematic showing a side view of the individual coaxialcables that are to be operatively coupled to the pair of Samtec BTH-090connectors on the flex circuit board via a pair of BSH-090 connectors;

FIG. 14 is a schematic showing an exemplary plan view of half of thecoaxial leads therein the cable connected to one of the BSH-090connectors;

FIG. 15A is an illustration of an exemplary plan view of the distal endof a medical cable assembly connected to the folded flex circuit board,the cable's proximal end (not shown) may include a multi-pin ZIFconnector that interfaces with the ultrasound system and may be used topractice one or more aspects of the present invention;

FIG. 15B illustrates an exemplary termination pin-out for the individualcoax cables of a medical cable assembly to a multi-pin ZIF connectorhaving an exemplary ZIF connector such as an ITT Cannon DLM6 connector;

FIG. 16 is a block diagram illustrating an exemplary high frequencyultrasonic imaging system;

FIG. 17 is a block diagram further illustrating the exemplary highfrequency ultrasonic imaging system shown in FIG. 16;

FIG. 18 a is a schematic diagram illustrating exemplary receivebeamformers, transmit beamformers, front end electronics, and associatedcomponents;

FIG. 18 b is an exemplary embodiment providing additional detail of thefront end electronics shown in FIG. 18 a;

FIG. 18 c is an exemplary embodiment of a receive controller (RXcontroller) in an embodiment according to the present invention

FIG. 18 d is an illustration of an exemplary transmit controller (TXcontroller) in an embodiment according to the present invention FIG. 19is a system signal processing block diagram illustrating an exemplarybeamformer control board;

FIG. 20 is a schematic diagram of a TX/RX Switch and Pulser and relatedcircuitry;

FIG. 21 is a schematic diagram of an alternative embodiment of a TX/RXSwitch and Pulser and related circuitry;

FIG. 22 is a block diagram for an exemplary transmit beamformer control;

FIGS. 22A-22C illustrate how exemplary waveshape data can be used tochange the fine delay, pulse width and dead time for “A” and “B”signals;

FIG. 24 illustrates a systems electronics overview of an exemplary highfrequency ultrasonic imaging system;

FIG. 25 shows an exemplary single channel delay scheme for quadraturesampling;

FIG. 25B is an alternative way of implementing interpolation filters,phase rotation and dynamic apodization according to an embodiment of theinvention;

FIG. 26 illustrates an exemplary control RAM for storing receive controlsignals;

FIG. 26A shows exemplary beamformer delay control signals for center andouter elements of an arrayed transducer;

FIG. 27 is a block diagram of an exemplary transmit/receivesynchronization scheme;

FIG. 27A is a block diagram of an alternate exemplary transmit/receivesynchronization scheme;

FIG. 28 illustrates an exemplary RF memory buffer for storage ofbeamformer output;

FIG. 29 illustrates an exemplary system software overview an exemplaryhigh frequency ultrasonic imaging system;

FIG. 30 is an exemplary main system software application overview for anexemplary high frequency ultrasonic imaging system;

FIG. 31 illustrates an exemplary modular system overview for anexemplary high frequency ultrasonic imaging system;

FIG. 32 displays an exemplary transmit frequency, half cycle on time,and pulse durations;

FIG. 33 illustrates exemplary bandwidth sampling of 30 MHz signalspectrum;

FIG. 34 illustrates an exemplary quadrature sampled sine wave at 0.9times the sample frequency;

FIG. 34A is an exemplary illustration of the 16 sample points of FIG. 34with respect to Q and I sampling points;

FIG. 34B is an exemplary illustration of a window of eight samples usedby an exemplary FIR filter for interpolation of points 0-3, between Qand I samples;

FIG. 34C is the exemplary window of FIG. 34 moved forward by one samplein order to interpolate points 4-15;

FIG. 35 displays exemplary interpolated points for I and Q waveforms;

FIG. 36 displays exemplary quadrature samples data set for single rayline acquisition from a linear array;

FIGS. 37A and 37B display two exemplary channel signals returned fromthe same range point, but with a path length difference corresponding toone-half wavelength;

FIG. 38 displays 3-1 multi-line scanning with an exemplary curved arraytransducer;

FIG. 39 displays a conceptual implementation of an interpolation delaymethod;

FIG. 40 displays an exemplary 3-1 multi-line operation of aninterpolation delay method; and

FIG. 41 is a schematic design of Complimentary Hilbert TransformFilters.

DETAILED DESCRIPTION

The present invention may be understood more readily by reference to thefollowing detailed description of the invention and the Examplesincluded therein and to the Figures and their previous and followingdescription.

Before the present compounds, compositions, articles, devices, and/ormethods are disclosed and described, it is to be understood that thisinvention is not limited to specific methods, specific components, or toparticular computer architecture, as such may, of course, vary. It isalso to be understood that the terminology used herein is for thepurpose of describing particular embodiments only and is not intended tobe limiting. As used in the specification and the appended claims, thesingular forms “a,” “an” and “the” include plural referents unless thecontext clearly dictates otherwise. Thus, for example, reference to “aprocessing unit,” or to “a receive channel” includes two or more suchprocessing units or receive channels, and the like.

Ranges may be expressed herein as from “about” one particular value,and/or to “about” another particular value. When such a range isexpressed, another embodiment includes from the one particular valueand/or to the other particular value. Similarly, when values areexpressed as approximations, by use of the antecedent “about,” it willbe understood that the particular value forms another embodiment. Itwill be further understood that the endpoints of each of the ranges aresignificant both in relation to the other endpoint, and independently ofthe other endpoint. “Optional” or “optionally” means that thesubsequently described event or circumstance may or may not occur, andthat the description includes instances where said event or circumstanceoccurs and instances where it does not.

Aspects of the exemplary systems disclosed herein can be implemented viaa general-purpose computing device such as one in the form of a computer101 shown in FIG. 1. The components of the computer 101 can include, butare not limited to, one or more processors or processing units 103, asystem memory 112, and a system bus 113 that couples various systemcomponents including the processor 103 to the system memory 112.

The system bus 113 represents one or more of several possible types ofbus structures, including a memory bus or memory controller, aperipheral bus, an accelerated graphics port, and a processor or localbus using any of a variety of bus architectures. By way of example, sucharchitectures can include an Industry Standard Architecture (ISA) bus, aMicro Channel Architecture (MCA) bus, an Enhanced ISA (EISA) bus, aVideo Electronics Standards Association (VESA) local bus, and aPeripheral Component Interconnects (PCI) bus also known as a Mezzaninebus. This bus, and all buses specified in this description can also beimplemented over a wired or wireless network connection. The bus 113,and all buses specified in this description can also be implemented overa wired or wireless network connection and each of the subsystems,including the processor 103, a mass storage device 104, an operatingsystem 105, application software 106, data 107, a network adapter 108,system memory 112, an Input/Output Interface 110, a display adapter 109,a display device 111, and a human machine interface 102, can becontained within one or more remote computing devices 114 a,b,c atphysically separate locations, connected through buses of this form, ineffect implementing a fully distributed system.

The computer 101 typically includes a variety of computer readablemedia. Such media can be any available media that is accessible by thecomputer 101 and includes both volatile and non-volatile media,removable and non-removable media. The system memory 112 includescomputer readable media in the form of volatile memory, such as randomaccess memory (RAM), and/or non-volatile memory, such as read onlymemory (ROM). The system memory 112 typically contains data such as data107 and/or program modules such as operating system 105 and applicationsoftware 106 that are immediately accessible to and/or are presentlyoperated on by the processing unit 103.

The computer 101 may also include other removable/non-removable,volatile/non-volatile computer storage media. By way of example, FIG. 1illustrates a mass storage device 104 which can provide non-volatilestorage of computer code, computer readable instructions, datastructures, program modules, and other data for the computer 101. Forexample, a mass storage device 104 can be a hard disk, a removablemagnetic disk, a removable optical disk, magnetic cassettes or othermagnetic storage devices, flash memory cards, CD-ROM, digital versatiledisks (DVD) or other optical storage, random access memories (RAM), readonly memories (ROM), electrically erasable programmable read-only memory(EEPROM), and the like.

Any number of program modules can be stored on the mass storage device104, including by way of example, an operating system 105 andapplication software 106. Each of the operating system 105 andapplication software 106 (or some combination thereof) may includeelements of the programming and the application software 106. Data 107can also be stored on the mass storage device 104. Data 104 can bestored in any of one or more databases known in the art. Examples ofsuch databases include, DB2®, Microsoft® Access, Microsoft® SQL Server,Oracle®, mySQL, PostgreSQL, and the like. The databases can becentralized or distributed across multiple systems.

A user can enter commands and information into the computer 101 via aninput device (not shown). Examples of such input devices include, butare not limited to, a keyboard, pointing device (e.g., a “mouse”), amicrophone, ajoystick, a serial port, a scanner, and the like. These andother input devices can be connected to the processing unit 103 via ahuman machine interface 102 that is coupled to the system bus 113, butmay be connected by other interface and bus structures, such as aparallel port, game port, or a universal serial bus (USB). In anexemplary system of an embodiment according to the present invention,the user interface can be chosen from one or more of the input deviceslisted above. Optionally, the user interface can also include variouscontrol devices such as toggle switches, sliders, variable resistors andother user interface devices known in the art. The user interface can beconnected to the processing unit 103. It can also be connected to otherfunctional blocks of the exemplary system described herein inconjunction with or without connection with the processing unit 103connections described herein.

A display device 111 can also be connected to the system bus 113 via aninterface, such as a display adapter 109. For example, a display devicecan be a monitor or an LCD (Liquid Crystal Display). In addition to thedisplay device 111, other output peripheral devices can includecomponents such as speakers (not shown) and a printer (not shown) whichcan be connected to the computer 101 via Input/Output Interface 110.

The computer 101 can operate in a networked environment using logicalconnections to one or more remote computing devices 114 a,b,c. By way ofexample, a remote computing device can be a personal computer, portablecomputer, a server, a router, a network computer, a peer device or othercommon network node, and so on. Logical connections between the computer101 and a remote computing device 114 a,b,c can be made via a local areanetwork (LAN) and a general wide area network (WAN). Such networkconnections can be through a network adapter 108. A network adapter 108can be implemented in both wired and wireless environments. Suchnetworking environments are commonplace in offices, enterprise-widecomputer networks, intranets, and the Internet 115. The remote computer114 a,b,c may be a server, a router, a peer device or other commonnetwork node, and typically includes all or many of the elements alreadydescribed for the computer 101. In a networked environment, programmodules and data may be stored on the remote computer 114 a,b,c. Thelogical connections include a LAN and a WAN. Other connection methodsmay be used, and networks may include such things as the “world wideweb” or Internet.

For purposes of illustration, application programs and other executableprogram components such as the operating system 105 are illustratedherein as discrete blocks, although it is recognized that such programsand components reside at various times in different storage componentsof the computing device 101, and are executed by the data processor(s)of the computer. An implementation of application software 106 may bestored on or transmitted across some form of computer readable media.Computer readable media can be any available media that can be accessedby a computer. By way of example, and not limitation, computer readablemedia may comprise “computer storage media” and “communications media.”Computer storage media include volatile and non-volatile, removable andnon-removable media implemented in any method or technology for storageof information such as computer readable instructions, data structures,program modules, or other data. Computer storage media includes, but isnot limited to, RAM, ROM, EEPROM, flash memory or other memorytechnology, CD-ROM, digital versatile disks (DVD) or other opticalstorage, magnetic cassettes, magnetic tape, magnetic disk storage orother magnetic storage devices, or any other medium which can be used tostore the desired information and which can be accessed by a computer.An implementation of the disclosed method may be stored on ortransmitted across some form of computer readable media.

The processing of the disclosed method can be performed by softwarecomponents. The disclosed method may be described in the general contextof computer-executable instructions, such as program modules, beingexecuted by one or more computers or other devices. Generally, programmodules include computer code, routines, programs, objects, components,data structures, etc. that perform particular tasks or implementparticular abstract data types. The disclosed method may also bepracticed in grid-based and distributed computing environments wheretasks are performed by remote processing devices that are linked througha communications network. In a distributed computing environment,program modules may be located in both local and remote computer storagemedia including memory storage devices.

Aspects of the exemplary systems shown in the Figures and describedherein, can be implemented in various forms including hardware,software, and a combination thereof. The hardware implementation caninclude any or a combination of the following technologies, which areall well known in the art: discrete electronic components, a discretelogic circuit(s) having logic gates for implementing logic functionsupon data signals, an application specific integrated circuit havingappropriate logic gates, a programmable gate array(s) (PGA), fieldprogrammable gate array(s) (FPGA), etc. The software comprises anordered listing of executable instructions for implementing logicalfunctions, and can be embodied in any computer-readable medium for useby or in connection with an instruction execution system, apparatus, ordevice, such as a computer-based system, processor-containing system, orother system that can fetch the instructions from the instructionexecution system, apparatus, or device and execute the instructions.

Aspects of the exemplary systems can be implemented in computerizedsystems. Aspects of the exemplary systems, including for instance thecomputing unit 101, can be operational with numerous other generalpurpose or special purpose computing system environments orconfigurations. Examples of well known computing systems, environments,and/or configurations that may be suitable for use with the system andmethod include, but are not limited to, personal computers, servercomputers, laptop devices, and multiprocessor systems. Additionalexamples include set top boxes, programmable consumer electronics,network PCs, minicomputers, mainframe computers, distributed computingenvironments that include any of the above systems or devices, and thelike.

Aspects of the exemplary systems can be described in the general contextof computer instructions, such as program modules, being executed by acomputer. Generally, program modules include routines, programs,objects, components, data structures, etc. that perform particular tasksor implement particular abstract data types. The system and method mayalso be practiced in distributed computing environments where tasks areperformed by remote processing devices that are linked through acommunications network. In a distributed computing environment, programmodules may be located in both local and remote computer storage mediaincluding memory storage devices.

Among many possible applications, the described embodiments enable invivo visualization, assessment, and measurement of anatomical structuresand hemodynamic function in longitudinal imaging studies of smallanimals. The systems can provide images having very high resolution,image uniformity, depth of field, adjustable transmit focal depths,multiple transmit focal zones for multiple uses. For example, theultrasound image can be of a subject or an anatomical portion thereof,such as a heart or a heart valve. The image can also be of blood and canbe used for applications including evaluation of the vascularization oftumors. The systems can be used to guide needle injections.

The described embodiments can also be used for human clinical, medical,manufacturing (e.g., ultrasonic inspections, etc.) or other applicationswhere producing an image at a transmit frequency of 15 MHz or higher isdesired.

Embodiments according to the described systems can comprise one or moreof the following, which are described in greater detail herein: an arraytransducer that can be operatively connected to a processing system thatmay be comprised of one or more of signal and image processingcapabilities; digital transmit and receive beamformer subsystems; analogfront end electronics; a digital beamformer controller subsystem; a highvoltage subsystem; a computer module; a power supply module; a userinterface; software to run the beamformer; a scan converter, and othersystem features as described herein.

An arrayed transducer used in the system can be incorporated into ascanhead that, in one embodiment, may be attached to a fixture duringimaging which allows the operator to acquire images free of thevibrations and shaking that usually result from “free hand” imaging. Asmall animal subject may also be positioned on a heated platform withaccess to anesthetic equipment, and a means to position the scanheadrelative to the subject in a-flexible manner. The scanhead can beattached to a fixture during imaging. The fixture can have variousfeatures, such as freedom of motion in three dimensions, rotationalfreedom, a quick release mechanism, etc. The fixture can be part of a“rail system” apparatus, and can integrate with the heated mouseplatform.

The systems can be used with platforms and apparatus used in imagingsmall animals including “rail guide” type platforms with maneuverableprobe holder apparatuses. For example, the described systems can be usedwith multi-rail imaging systems, and with small animal mount assembliesas described in U.S. patent application Ser. No. 10/683,168, entitled“Integrated Multi-Rail Imaging System,” U.S. patent application Ser. No.10/053,748, entitled “Integrated Multi-Rail Imaging System,” U.S. patentapplication Ser. No. 10/683,870, now U.S. Pat. No. 6,851,392, issuedFeb. 8,2005, entitled “Small Animal Mount Assembly,” and U.S. patentapplication Ser. No. 11/053,653, entitled “Small Animal Mount Assembly,”which are each fully incorporated herein by reference.

Small animals can be anesthetized during imaging and vital physiologicalparameters such as heart rate and temperature can be monitored. Thus, anembodiment of the system may include means for acquiring ECG andtemperature signals for processing and display. An embodiment of thesystem may also display physiological waveforms such as an ECG,respiration or blood pressure waveform.

OVERVIEW

Provided herein are embodiments of a system for acquiring ultrasoundsignals comprising a signal processing unit adapted for acquiring areceived ultrasound signal from an ultrasound transducer having aplurality of elements. The system can be adapted to receive ultrasoundsignals having a frequency of at least 15 megahertz (MHz) with atransducer having a field of view of at least 5.0 millimeters (mm) at aframe rate of at least 20 frames per second (fps). In other embodiments,the ultrasound signals can be acquired at an acquisition rate of 50,100, or 200 (fps). Optionally, ultrasound signals can be acquired at anacquisition rate of 200 frames per second (fps) or higher. In otherexamples, the received ultrasound signals can be acquired at a framerate within the range of about 100 fps to about 200 fps. In someexemplary aspects, the length of the transducer is equal to the field ofview. The field of view can be wide enough to include organs of interestsuch as the small animal heart and surrounding tissue for cardiology,and full length embryos for abdominal imaging. In one embodiment, thetwo-way bandwidth of the transducer can be approximately 50% to 100%.Optionally, the two-way bandwidth of the transducer can be approximately60% to 70%. Two-way bandwidth refers to the bandwidth of the transducerthat results when the transducer is used both as a transmitter ofultrasound and a receiver—that is, the two-way bandwidth is thebandwidth of the one-way spectrum squared.

The processing unit produces an ultrasound image from the acquiredultrasound signal(s). The acquired signals may be processed to generatean ultrasound image at display rate that is slower than the acquisitionrate. Optionally, the generated ultrasound image can have a display rateof 100 fps or less. For example, the generated ultrasound image has adisplay rate of 30 fps or less. The field of view can range from about2.0 mm to about 30.0 mm. When a smaller field of view is utilized, theprocessing unit can acquire the received ultrasound signals at anacquisition rate of at least 300 frames per second (fps). In otherexamples, the acquisition rate can be 50, 100, 200 or more frames persecond (fps).

In one embodiment, in which a 30 MHz center frequency transducer isused, the image generated using the disclosed systems may have a lateralresolution of about 150 microns (μm) or less and an axial resolution ofabout 75 microns (μm) or less. For example, the image can have an axialresolution of about 30 microns (μm). Furthermore, embodiments accordingto the present invention transmit ultrasound that may be focused at adepth of about 1.0 mm to about 30.0 mm. For example, the transmittedultrasound can be focused at a depth of about 3.0 mm to about 10.0 mm.In other examples, the transmitted ultrasound can be focused at a depthof about 2.0 mm to about 12.0 mm, of about 1.0 mm to about 6.0 mm, ofabout 3.0 mm to about 8.0 mm, or of about 5.0 mm to about 30.0 mm.

Transducers

In various embodiments, the transducer can be, but is not limited to, alinear array transducer, a phased array transducer, a two-dimensional(2-D) array transducer, or a curved array transducer. A linear array istypically flat, i.e., all of the elements lie in the same (flat) plane.A curved linear array is typically configured such that the elements liein a curved plane. The transducers described herein are “fixed”transducers. The term “fixed” means that the transducer array does notutilize movement in its azimuthal direction during transmission orreceipt of ultrasound in order to achieve its desired operatingparameters, or to acquire a frame of ultrasound data. Moreover, if thetransducer is located in a scanhead or other imaging probe, the term“fixed” may also mean that the transducer is not moved in an azimuthalor longitudinal direction relative to the scan head, probe, or portionsthereof during operation. The described transducers, which are fixed asdescribed, are referred to throughout as an “array,” a “transducer,” an“ultrasound transducer,” an “ultrasound array,” an “array transducer,”an “arrayed transducer,” an “ultrasonic transducer” or combinations ofthese terms, or by other terms which would be recognized by thoseskilled in the art as referring to an ultrasound transducer. Thetransducers as described herein can be moved between the acquisition ofultrasound frames, for example, the transducer can be moved between scanplanes after acquiring a frame of ultrasound data, but such movement isnot required for their operation. As one skilled in the art wouldappreciate however, the transducer of the present system can be movedrelative to the object imaged while still remaining fixed as to theoperating parameters. For example, the transducer can be moved relativeto the subject during operation to change position of the scan plane orto obtain different views of the subject or its underlying anatomy.

Arrayed transducers are comprised of a number of elements. In oneembodiment, the transducer used to practice one or more aspects of thepresent invention comprises at least 64 elements. In one aspect, thetransducer comprises 256 elements. The transducer can also comprisefewer or more than 256 elements. The transducer elements can beseparated by a distance equal to about one-half the wavelength to abouttwo times the wavelength of the center transmit frequency of thetransducer (referred to herein as the “element pitch.”). In one aspect,the transducer elements are separated by a distance equal to about thewavelength of the center transmit frequency of the transducer.Optionally, the center transmit frequency of the transducer used isequal to or greater than 15 MHz. For example, the center transmitfrequency can be approximately 15 MHz, 20, MHz, 30 MHz, 40 MHz, 50 MHz,55 MHz or higher. In some exemplary aspects, the ultrasound transducercan transmit ultrasound into the subject at a center frequency withinthe range of about 15 MHz to about 80 MHz. In one embodiment accordingto the present invention, the transducer has a center operatingfrequency of at least 15 MHz and the transducer has an element pitchequal to or less than 2.0 times the wavelength of sound at thetransducer's transmitted center frequency. The transducer can also havean element pitch equal to or less than 1.5 times the wavelength of soundat the transducers transmitted center frequency.

By non-limiting example, one transducer that maybe used with thedescribed system can be, among others, an arrayed transducer asdescribed in U.S. patent application Ser. No. 11/109,986, entitled“Arrayed Ultrasonic Transducer,” filed Apr. 20, 2005 and published onDec. 8, 2005 as U.S. Patent Application Publication No.: US 2005/0272183A1, which is fully incorporated herein by reference and made a parthereof. The transducer may also comprise an array of piezoelectricelements which can be electronically steered using variable pulsing anddelay mechanisms. The processing system according to various embodimentsof the present invention may include multiple transducer ports for theinterface of one or more transducers or scanheads. As previouslydescribed, a scanhead can be hand held or mounted to rail system and thescanhead cable can be flexible.

Whether the system includes a transducer, or is adapted to be used witha separately acquired transducer, each element of the transducer can beoperatively connected to a receive channel of a processing unit.Optionally, the number of transducer elements is greater than the numberof receive channels. For example, the transducer may comprise at least64 elements that are operatively connected to at least 32 receivechannels. In one aspect, 256 elements are operatively connected to 64receive channels. In another aspect, 256 elements are operatively Iconnected to 128 receive channels. In yet another aspect, 256 elementsare operatively connected to 256 receive channels. Each element can alsobe operatively connected to a transmit channel.

Sampling

The system can further comprise one or more signal samplers for eachreceive channel. The signal samplers can be analog-to-digital converters(ADCs). The signal samplers can use direct sampling techniques to samplethe received signals. Optionally, the signal samplers can use bandwidthsampling to sample the received signals. In another aspect, the signalsamplers can use quadrature sampling to sample the received signals.Optionally, with quadrature sampling, the signal samplers comprisesampling clocks shifted 90 degrees out of phase. Also with quadraturesampling the sampling clocks also have a receive period, and the receiveclock frequency can be approximately equal to the center frequency of areceived ultrasound signal but may be different from the transmitfrequency. For example, in many situations, the center frequency of thereceived signal has been shifted lower than the center frequency of thetransmit signal due to frequency dependent attenuation in the tissuebeing imaged. For these situations the receive sample clock frequencycan be lower than the transmit frequency.

An acquired signal can be processed using an interpolation filtrationmethod. Using the interpolation filtration method a delay resolution canbe used, which can be less than the receive clock period. In anexemplary aspect, the delay resolution can be, for example, 1/16 of thereceive clock period.

The processing unit can comprise a receive beamformer. The receivebeamformer can be implemented using at least one field programmable gatearray (FPGA) device. The processing unit can also comprise a transmitbeamformer. The transmit beamformer can also be implemented using atleast one FPGA device.

In one aspect, 512 lines of ultrasound are generated, transmitted intothe subject and received from the subject for each frame of thegenerated ultrasound image. In a further aspect, 256 lines of ultrasoundcan also be generated, transmitted into the subject and received fromthe subject for each frame of the generated ultrasound image. In anotheraspect, at least two lines of ultrasound can be generated, transmittedinto the subject and received from the subject at each element of thearray for each frame of the generated ultrasound image. Optionally, oneline of ultrasound is generated, transmitted into the subject andreceived from the subject at each element of the array for each frame ofthe generated ultrasound image.

The ultrasound systems described herein can be used in multiple imagingmodes. For example, the systems can be used to produce an image inB-mode, M-mode, Pulsed Wave (PW) Doppler mode, power Doppler mode, colorflow Doppler mode, RF-mode and 3-D mode. The systems can be used inColor Flow Imaging modes, including directional velocity color flow,Power Doppler imaging and Tissue Doppler imaging. The systems can alsobe used with Steered PW Doppler, with very high pulse repetitionfrequencies (PRF). The systems can also be used in M-Mode, withsimultaneous B-Mode, for cardiology or other applications where suchtechniques are desired. The system can optionally be used in Duplex andTriplex modes, in which M-Mode and PW Doppler and/or Color Flow modesrun simultaneously with B-Mode in real-time. A 3-D mode in which B-Modeor Color Flow mode information is acquired over a 3-dimensional regionand presented in a 3-D surface rendered display can also be used. A linebased image reconstruction or “EKV” mode, can be used for cardiology orother applications, in which image information is acquired over severalcardiac cycles and recombined to provide a very high frame rate display.Line based image reconstruction methods are described in U.S. patentapplication Ser. No. 10/736,232, now U.S. Pat. No. 7,052,460 issued May30, 2006 and entitled “System for Producing an Ultrasound Image UsingLine Based Image Reconstruction,” which is incorporated fully herein byreference and made a part hereof. Such line based imaging methods imagecan be incorporated to produce an image when a high frame acquisitionrate is desirable, for example when imaging a rapidly beating mouseheart. In the RF acquisition mode, raw RF data can be acquired,displayed and made available for off-line analysis.

In one embodiment, the transducer can transmit at a pulse repetitionfrequency (PRF) of at least 500 hertz (Hz). The system can furthercomprise a processing unit for generating a color flow Dopplerultrasound image from the received ultrasound. Optionally, the PRF isbetween about 100 Hz to about 150 KHz. In M-Mode or RF Mode the PRF isbetween about 100 Hz and about 10 KHz. For Doppler modes, the PRF can bebetween about 500 Hz and about 150 KHz. For M-Mode and RF mode, the PRFcan be between about 50 Hz and about 10 KHz.

Exemplary Arrayed Transducer

Referring now to FIGS. 2A-15B, a circuit board according to anembodiment of the present invention is adapted to accept an exemplarytransducer and that is further adapted to connect to at least oneconventional connector. As noted herein, the conventional connector canbe adapted to complementarily connect with a cable for transmissionand/or supply of required signals. With regard to the figures, due tothe fine detail of the circuit board and unless otherwise indicated, thefigures are merely representative of complementary circuit boards andassociated multi element arrays. FIGS. 5A-5C show various views of anexemplary circuit board for a 256 element array having a 75 micronpitch.

Referring now in particular to FIGS. 2A-4B, an exemplary transducer foruse with the exemplary circuit board is illustrated. In FIGS. 2A-4B,exemplary top, bottom and cross-sectional views of an exemplaryschematic PZT stack are shown. FIG. 2A shows a top view of the PZT stackand illustrates portions of the ground electric layer that extend fromthe top and bottom portions of the PZT stack. In one aspect, the groundelectric layer extends the full width of the PZT stack. FIG. 2B shows abottom view of the PZT stack. In this aspect, along the longitudinallyextending edges of the PZT stack, the PZT stack forms exposed portionsof the dielectric layer between individual signal electrode elements. Inanother aspect, the signal elements extend the full width of the PZTstack. As one will appreciate, not shown in the underlying “centerportion” of the PZT stack are lines showing the individualized signalelectrode elements. As one will further appreciate, there is one signalelectrode per element of the PZT stack, e.g., 256 signal electrodes fora 256-element array.

FIG. 3A is a top plan view of an interposer for use with the PZT stackof FIGS. 2A-C, comprising electrical traces extending outwardly fromadjacent the central opening of the interposer. The interposer furthercomprises ground electrical traces located at the top and bottomportions of the piece.

The interposer can further comprise a dielectric layer disposed thereona portion of the top surface of the interposer about the central openingof the piece. In this aspect, and referring also to FIG. 3B, thedielectric layer defines two arrays of staggered wells, one array beingon each side of the central opening and extending along an axis parallelto the longitudinal axis of the interposer. Each well is incommunication with an electrical trace of the interposer. A solder pastecan be used to fill each of the wells in the dielectric layer such that,when a PZT stack is mounted thereon the dielectric layer and heat isapplied, the solder melts to form the desired electrical continuitybetween the individual element signal electrodes and the individualtrances on the interposer. In use, the well helps to retain the solderwithin the confines of the well.

FIG. 4A is a top plan view of the PZT stack shown in FIG. 2A mountedthereon the dielectric layer of the interposer shown in FIG. 3A. To aidin the understanding of the invention, FIG. 4B provides a top plan viewof the PZT stack shown in FIG. 2A mounted thereon the dielectric layerand interposer shown in FIG. 3A, in which the PZT stack is shown as atransparency. This provides an illustration of the mounting relationshipbetween the PZT stack and the underlying dielectric layer/interposer,the solder paste mounted therebetween forming an electrical connectionbetween the respective element signal electrodes and the electricaltraces on the interposer.

Referring now to FIG. 5A, a schematic top plan view of an exemplarycircuit board for mounting the transducer of the present inventionthereto is illustrated. In one aspect, at least a portion of the circuitboard can be flexible. In one embodiment, the circuit board comprising abottom copper ground layer and a Kapton™ layer mounted to the uppersurface of the bottom copper ground layer. In one aspect, the circuitboard can also comprise a plurality of underlying substantially rigidsupport structures. In this aspect, a central portion surrounding acentral opening in the circuit board can have a rigid support structuremounted to the bottom surface of the bottom copper ground layer. In afurther aspect, portions of the circuit board to which the connectorscan be attached also have rigid support structures mounted to the bottomsurface of the bottom copper ground layer.

The circuit board further comprise a plurality of board electricaltraces formed thereon the top surface of the KaptonT layer, each boardelectrical trace having a proximal end adapted to couple to anelectrical trace of the transducer and a distal end adapted to couple toa connector, such as, for example, a cable for communication of signalstherethrough. In one aspect, the length of the circuit forming eachelectrical trace has a substantially constant impedance.

The circuit board also comprises a plurality of vias that pass thoughthe Kapton™ layer and are in communication with the underlying groundlayer so that signal return paths, or signal ground paths, can beformed. Further, the circuit board comprises a plurality of ground pins.Each ground pin has a proximal end that is coupled to the ground layerof the circuit board (passing through one of the vias in the Kaptonlayer) and a distal end that is adapted to couple to the connector.

FIG. 5B is a top plan view of an exemplary circuit board for mounting ofan exemplary 256-element array having a 75 micron pitch and FIG. 5C is atop plan view of the vias of the circuit board of FIG. 5B that are incommunication with an underlying ground layer of the circuit board. FIG.5B also defines bores in the circuit board that are sized and shaped toaccept pins of the connectors such that, when the connector is mountedthereon portions of the circuit board, there will be correctregistration of the respective electrical traces and ground pins withthe connector.

FIG. 6 illustrates a partial enlarged top plan view of a portion of theexemplified circuit board showing, in Region A, the ground electrodelayer of the transducer being wire bonded to an electrical trace on theinterposer, which can be, in turn, wire bonded to ground pads of thecircuit board. The ground pads of the circuit board are incommunication, through vias in the Kapton™ layer, with the underlyingbottom copper ground layer. As illustrated, in Region B, the individualelectrical traces of the transducer are wire bonded to individual boardelectrical traces of the circuit board. Referring now to FIG. 8A, in oneaspect the central opening of the circuit board underlies the backingmaterial of the transducer. FIG. 7A is an enlarged partial view Region Bof an exemplified transducer mounted to a portion of the circuit board.

Referring now to FIGS. 11A-11B, a transducer mounting is shown that doesnot include an interposer to the substantially rigid central portion ofthe circuit board. This embodiment allows for the elimination of most ofthe wire bonds. In this aspect, the PZT stack is surface mounted ontothe circuit board directly by, for example, means of a series of goldball bumps. The gold ball bump means is a conventional surface mountingtechnique and represents another type of surface mounting techniquesconsistent with the previously mentioned surface mounting techniques. Inthis example, the rigidized central portion of the circuit board canprovide the same functionality as the interposer. Wire bonds, or otherelectrical connection, from the ground electrode of the PZT stack to theground of the circuit board are still required to compete the signalreturn of the assembled device. FIG. 11A shows the ground electrodelayer of the transducer (without interposer) wire bonded to the groundpads of the circuit board.

In one aspect, the gold ball bumps are applied directly onto the circuitboard. Each ball bump is positioned in communication with one electricaltrace of the circuit board. When the PZT stack is applied, it is alignedwith the electrical traces of the circuit board and electricalcontinuity is made via the ball bumps. The PZT stack is secured to thecircuit board by, for example and not meant to be limiting, a) use of anunderfill, such as a UV curable; b) use of an ACF tape; c) byelectroplating pure Indium solder onto the electrodes of either the PZTor the circuit board and reflowing the Indium to provide a solderjointbetween the signal electrode on the PZT and the gold ball bump on thecircuit board, and the like.

An arrayed transducer can be operatively connected to the processingunit of the system using the flex circuit as shown in FIGS. 2A-11.Referring now to FIGS. 12-15, the flex circuit can be operativelyconnected with a BTH connector. BTH connectors are common and areavailable in a variety of sizes. The BTH connector comprises a number ofpins for mating with a BSH connector. The number of pins can be at leastone greater than the number of array elements or traces of flex. Forexample, the number pins can be equal twice the number of array elementsor corresponding traces of flex. Thus, in one example, 2×180=360 pinscan be used for the 256 traces on the flex circuit of a 256 elementarray. In another example, 256 pins can be used for the exemplary 256element array. The BSH connector can be connectively seated within theBTH. The BSH connector is operatively connected with an interface suchas a printed circuit board that is terminated with a plurality ofcoaxial cables. A larger common cable formed from the plurality ofcoaxial cables can be terminated with a ZIF end for interfacing with theprocessing unit of the ultrasound system at a ZIF receptacle orinterfacing site. One exemplary ZIF connector that can be used is a 360Pin DLM6 ITT Cannon ZIF™ connector as available from ITT Corporation ofWhite Plains, N.Y. As would be clear to one skilled in the art, however,alternative ZIF™ connectors can be used for interfacing with theprocessing unit and can have more or less than 360 pins.

The connection can comprise a cable or bundle of cables. The cable canconnect each element of the array to the processing unit in a one-to-onerelationship; that is, each element can be electrically connected withits own signal and a ground lead to a designated connection point in theprocessing unit whereby the plurality of individual element connectionsare bundled together to form the overall cable. Optionally, eachindividual electrical connection can be unbundled and not physicallyformed into a cable or cable assembly.

Suitable cables can be coaxial cables, twisted pairs, and copper alloywiring. Other connection means can be via non-physically connectedmethods such as RF links, infrared links, and similar technologies whereappropriate transmitting and receiving components are included.

The individual element connections can comprise coaxial cable of a typetypically used for connection array elements to processing units. Thesecoaxial cables can be of a low loss type. The coaxial cables typicallycomprise a center conductor and some type of outer shielding insulatedfrom the center conductor and encased in an outer layer of insulation.These coaxial cables can have nominal impedances appropriate for usewith an array. Example nominal impedances can be 50 ohms or more,including 50 ohms, 52 ohms, 73 ohms, 75 ohms or 80 ohms.

An exemplary medical cable for use with one or more of the ultrasoundimaging systems described herein comprises a minimum of 256 coaxialcables of 40 AWG with a nominal impedance of about 75 ohms with coaxialcable lengths of about 2.0 m. The length can be less than 2.0 m orgreater than 2.0 m. The medical cable jacket length can accommodate thecable length, can include additional metal sheaths for electricalshielding and can be made of PVC or other flexible materials.

Cables and the connections for connecting an array transducer to theprocessing unit, including those described herein can be fabricated bycompanies such as Precision Interconnect-TYCO Electronics (TycoElectronics Corporation, Wilmington, Del.).

The exemplary cable, at the proximal end, can further comprise offlex/strain relief, 12 PCBs interfacing between the coaxial cables andthe ZIF™ pins, a 360 Pin ITT Cannon ZIF™ connector and actuation handle(DLM6-360 type), and a shielded casing around the connector. Theexemplary cable, at the distal end, can comprise of a flex/strain reliefcable terminated to two PCBs, interfacing between the coaxial cables andthe flex circuit board, wherein each PCB has 1 BSH-090-01-L-D-A SamtecConnector (Samtec, Inc., New Albany, Ind.) and each PCB has 75 Ohmcharacteristic impedance traces with cables terminated from both sidesof the PCB in a staggered layout.

The cable can use a “flex circuit” method of securing and connecting aplurality of coax cables which comprise the large cable. In an exemplaryembodiment, the array has 256-elements. The array is mounted in thecentral region of a flex circuit. The flex circuit has two ends suchthat the odd numbered elements 1,3,5,7 . . . 255 are terminated on theleft end of the flex with a BTH-090 connector labeled J1, and that theeven numbered elements 2,4,6,8. . . 256 are terminated on the right endof the flex with a BTH-090 connector labeled J3. For both ends, theelements are terminated in sequence along the upper and bottom rows oftheir respective connectors with GND (signal return) pins evenlydispersed across the connector in a repeated pattern.

The repeat pattern is defined from the outer edge of the flex towardsthe central region of the flex and is as follows:

-   -   2 signal pins, GND    -   3 signal pins, GND    -   2 signal pins, GND    -   3 signal pins . . . . . . , GND    -   3 signal pins, GND    -   2 signal pins, GND    -   2 signal pins, GND.

A schematic showing a side view of the folded flex circuit, with thearray mounted in the central array of the flex is shown in FIG. 12A andan associated pin out table for the connectors on the flex circuit isshown in FIG. 12B.

The flex circuit can be connected to the exemplary cable describedabove. The flex circuit can be connected to a PrecisionInterconnect-Tyco Electronics medical cable assembly. The electrical,for example, connection from the flex to the ZIF™ connector can be madethrough two scanhead PCBs followed by a coax cable bundle and 12 shortPCBs each with a 2×15 connector inserted into ZIF™ pins.

Each scanhead PCB (total of two) can comprise one BSH-090 connector, 128traces (all traces with controlled impedance of for example 75 Ohms at30 MHz) and can be terminated with 128 (40 AWG 75 Ohm) coax cables. ThePCB can have outer dimensions of 0.525″ by 2.344.″

FIG. 13 illustrates the design of the two scanhead PCBs. FIG. 14illustrates how the PCBs can be connected to the flex circuit andillustrates the staggered nature of how the coax cable ribbons can besoldered to the PCB. There are two scanhead PCBs. The left board can beconnected to the J1 connector on the flex and the right board can beconnected to the J3 connector. Each scanhead PCB can have one BSH-090connector. The pin-out for each scanhead trace can be matched to the pinout for the J1 and J3 connector.

ZIF Connector

An exemplary medical cable, as partially shown in FIG. 15A, comprises aZIF connector on the proximal end, the end of the cable which connectsto the processing unit. One skilled in the art will appreciate thatseveral designs of cable assemblies are possible. FIG. 15B illustrates apin out that can be used for the exemplary ZIF Connector. The pinslabeled as G are signal return pins. The pins labeled as N/C are notterminated with coaxial cables and these pins are reserved to be used aseither for shielding to chassis ground or for other unspecifiedfunctions. The N/C pins can be accessible by simply removing the ZIFhousing and soldering to the unused traces on any of the 12 PCBsconnected to the ZIF.

The 12 individual PCBs used to connect to the ZIF connector have coaxcables connected on one or both sides of the board. One edge of the PCBcan have a connector suitable for insertion into the ZIF connector(Saintec SSW or equivalent) and each PCB shall have the appropriatetraces and vias required to connect the correct coaxial cable to thecorrect ZIF pin.

Each PCB can have a Samtec SSW, or equivalent, connector with two rowsof 15 pins, although the number of coax cables may differ on some of the12 PCBs as defined in the FIG. 15B. The general layout of the pins onthe 2×15 connector is universal and is shown in Table 1.

One of the 12 PCBs requires provisions in the trace layout to include anEEPROM as defined in FIG. 15B. Two of the 12 PCBs require some of thepins to be terminated as required to provide the hard-coded PROBE IDnumber that will identify the particular array design included insidethe array assembly.

Various connection methods can be used including connectors of variousstyles. For these various connection methods, the impedance can be 75Ohms at a center frequency of 30 MHz. TABLE 1 The layout of connectionson the connector end of the ZIF PCB that plugs into the ITT Connector.General Pattern Signal Signal Signal GND Signal Signal GND Signal SignalSignal Signal Signal Signal GND Signal Signal GND Signal Signal SignalSignal Signal Signal GND Signal Signal GND Signal Signal Signal

Ultrasound System

An exemplary embodiment of an ultrasound system 1600 according to thepresent invention is shown in FIG. 16. FIG. 16 is a block diagramillustrating an exemplary high frequency ultrasonic imaging system 1600.The blocks shown in the various Figures can be functionalrepresentations of processes that take place within an embodiment of thesystem 1600. In practice, however, the functions may be carried outacross several locations or modules within the system 1600.

The exemplary system 1600 comprises an array transducer 1601, a cable1619, and a processing unit 1620. The cable 1619 connects the processingunit 1620 and the array transducer 1601. The processing unit maycomprise software and hardware components. The processing unit cancomprise one or more of a multiplexer(MUX)/front end electronics 1602, areceive beamformer 1603, a beamformer control 1604, a transmitbeamformer 1605, a system control 1606, a user interface 1607, a scanconverter 1608, a video processing display unit 1609, and processingmodules including one or more of a M-mode processing module (not shown),a PW Doppler processing module 1611, a B-mode processing module 1612, acolor flow processing module 1613, a 3-D mode processing module (notshown), and a RF mode processing module 1615. The center frequency rangeof the exemplary system can-be about 15-55 MHz or higher. When measuredfrom the outside edge of the bandwidths, the frequency range of theexemplary system can be about 10-80 MHz or higher.

The array transducer 1601 interfaces with the processing unit 1620 atthe MUX/front end electronics (MUX/FEE) 1602. The MUX portion of theMUX/FEE 1602 is a multiplexer which can electronically switch or connecta plurality of electrical paths to a lesser number of electrical paths.The array transducer 1601 converts electrical energy to ultrasoundenergy and vice versa and is electrically connected to the MUX/FEE 1602.

The MUX/FEE 1602 comprises electronics which generate a transmitwaveform which is connected to a certain subset of the elements of thearray, namely the elements of the active aperture. The subset ofelements is called the active aperture of the array transducer 1601. Theelectronics of the MUX/FEE 1602 also connects the active aperture of thearray to the receive channel electronics. During operation, the activeaperture moves about the array transducer 1601, in a manner determinedby components described herein.

The MUX/FEE 1602 switchably connects the elements of the active apertureto transmit and receive channels of the exemplary system. In anexemplary 256-element array transducer embodiment of the invention,there are 64 transmit channels and 64 receive channels that can beswitchably connected to the active aperture of up to 64 elements. The upto 64 elements of the active aperture are contiguous. In certainembodiments of the invention, there is a separate transmit MUX and aseparate receive MUX. Other embodiments of the invention share the MUXfor both the transmit channels and the receive channels.

During a transmit cycle of the exemplary ultrasound system 1600, thefront end electronics portion of the MUX/FEE 1602 supply a high voltagesignal to the elements of the active aperture of the array transducer1601. In one aspect, the front end electronics can also provideprotection circuitry for the receiver channels to protect them from thehigh voltage transmit signal, as the receive channels and the transmitchannels have a common connection point at the elements of the arraytransducer 1601. The protection can be in the form of isolationcircuitry which limits the amount oftransmit signal that can leak orpass into the receive channel to a safe level which will not causedamage to the receive electronics. Characteristics of the MUX/FEE 1602include a fast rise time on the transmit side, and high bandwidth on thetransmit and receive channels.

The MUX/FEE 1602 passes signals from the transmit beamformer 1605 to thearray transducer 1601. In an exemplary embodiment, the transmitbeamformer 1605 generates and supplies separate waveforms to each of theelements of the active aperture. In an exemplary embodiment, thewaveform for each element of the active aperture is the same. In anotheraspect, the waveforms for each element of the active aperture are notall the same and in some embodiments have differing center frequencies.

In one exemplary embodiment, each separate transmit waveform has a delayassociated with it. The distribution of the delays for each element'swaveform is called a delay profile. The delay profile is calculated in away to cause the desired focusing of the transmit acoustic beam to thedesired focal point. In certain embodiments, the transmit acoustic beamaxis is perpendicular to the plane of the array 1601, and the beam axisintersects the array 1601 at the center of the active aperture of thearray transducer 1601. The delay profile can also steer the beam so thatit is not perpendicular to the plane of the array 1601. In an exemplaryaspect of the present invention, a delay resolution of 1/16 can be used.Or, in other words, 1/16 of the period of the center frequency of thetransmit center frequency, though other delay resolutions arecontemplated within the scope of this invention. For example at a 50 MHzcenter frequency, the period is 20 nanoseconds, so 1/16 of that periodis 1.25 nanoseconds, which is the exemplarydelayresolution used to focusthe acoustic beam. It is to be appreciated that the delay resolution maybe different than 1/16^(th) of a period, for example delay resolutionsless than 1/16^(th) (e.g., 1/24, 1/32, etc) as well as delay resolutionsgreater than 1/16 (e.g., 1/12, ⅛, etc.) are contemplated within thescope of this invention.

The receive beamformer 1603, can also be connected to elements of theactive aperture of the array transducer 101 via the MUX/FEE 1602. Duringtransmit an acoustic signal penetrates into the subject and generates areflected signal from the tissues of the subject. The reflected signalis received by the elements of the active aperture of the arraytransducer 1601 and converted into an analog electrical signal emanatingfrom each element of the active aperture. The electrical signal issampled to convert it from an analog to a digital signal in the receivebeamformer 1603. Embodiments of the invention use quadrature samplingfor digitization of the received signal. During the receive cycle of thesystem 1600, the array transducer 1601 also has a receive aperture thatis determined by the beamformer control 1604, which tells the receivebeamformer 1603 which elements of the array to include in the activeaperture and what delay profile to use. The receive beamformer 1603 ofthe exemplary embodiment is a digital beamformer.

The receive beamformer 1603 introduces delays into the received signalof each element of the active aperture. The delays are collectivelycalled the delay profile. The receive delay profile can be dynamicallyadjusted based on time-of-flight—that is, the length of time that haselapsed during the transmission of the ultrasound into the tissue beingimaged. The time-of-flight is used to focus the receive beamformer to apoint of focus within the tissue. In other words, the depth of thereceive beam is adjusted using a delay profile which incorporatesinformation pertaining to the time-of-flight of the transmitted beam.

The received signal from each element of the active aperture is summedwherein the surn incorporates the delay profile. The summed receivedsignal flows along the receive channel from the receive beamformer 1603to one or more of the processing module(s) 1611, 1612, 1613, and/or1615, including those not shown in FIG. 16), as selected by the userinterface 1607 and system controls 1606, which act based upon a userinput.

The beam former control 1604 is connected to the MUX/FEE 1602 throughthe transmit beamformer 1605 and the receive beamformer 1603. It is alsoconnected to the system control 1606. The beamformer control 1604provides information to the MUX/FEE 1602 so that the desired elements ofthe array transducer 1601 are connected to form the active aperture. Thebeamformer control 1604 also creates and sends to the receive beamformer1603 the delay profile for use with the reception of a particular beam.In embodiments of the invention, the receive delay profile can beupdated repeatedly based upon the time of flight. The beamformer control1604 also creates and sends to the transmit beamformer 1605 the transmitdelay profile.

The system control 1606 operates in a manner known to one of ordinaryskill in the art. It takes input from the user interface 1607 andprovides the control information to the various components of the system1600 in order to configure the system 1600 for a chosen mode ofoperation. The scan converter 1608 operates in a manner known in the artand takes the raw image data generated from the one or more of theprocessing modules and converts the raw image data into an image thatcan be displayed by the video processing/display 1609. For someprocessing modes of operation, the image can be displayed without usingthe scan converter 1608 if the video characteristics of the image arethe same as those of the display.

The processing modules, except as noted herein, function in a mannerknown to one of ordinary skill in the art. For the PW Doppler module1611 and the color flow processing module 1613, the pulse repetitionfrequency (PRF) can be high due to the high center frequencies ofembodiments of this invention. The maximum unaliased velocities whichmay be measured are proportional to the PRF and inversely proportionalto the transmit center frequency. The PRFs required to allow for theunaliased measurement of specific velocities given specific transmitcenter frequencies may be calculated in a method known to one ofordinary skill in the art. Given that the transmit center frequenciesused are in the range of 15 to 55 MHz, or higher, and the blood flowvelocities can be as high as 1 m/s and in some cases greater than 1 m/sunaliased measurement of the Doppler signal resulting from thosevelocities will require the PRF for PW Doppler to be up to 150 KHz.Embodiments of the invention have a PW Doppler mode which supports PRFsup to 150 KHz, which for a center frequency of 30 MHz allows forunaliased measurement of blood velocities up to 1.9 m/s in mice with azero degree angle between the velocity vector of the moving target andthe ultrasound beam axis.

In certain embodiments, the RF module 1615 uses interpolation. If thesampling method used is quadrature sampling, then the RF signal may bereconstructed from the quadrature baseband samples by zero padding andfiltering, as would be known to one of ordinary skill in the art. IfNyquist sampling is used, then no reconstruction is required since theRF signal is sampled directly. In certain embodiments, the RF module1615 reconstructs the RF signal from the quadrature samples of thereceive beamformer output. The sampling takes place at the centerfrequency of the receive signal, but in quadrature, giving a basebandquadrature representation of the signal. The RF signal is created byfirst zero padding the quadrature sampled data stream, with the numberof zeros determined by the desired interpolated signal sample rate.Then, a complex bandpass filter is applied to the zero padded datastream, which rejects the frequency content of the zero padded signalthat is outside the frequency band from fs/2 to 3fs/2, where fs is thesample frequency. The result after filtering is a complex representationof the original RF signal. The RF signal is then passed on to the maincomputer unit for further processing such as digital filtering andenvelope detection and display. The real part or the complexrepresentation of the RF signal may be displayed. For example, the RFdata acquired for a particular scan line may be processed and displayed.Alternatively, RF data from a certain scan line averaged over a numberof pulse echo relurns can be displayed, or RF data acquired from anumber of different scan lines can be averaged and displayed. The scanlines to be used for acquisition of the RF data can be specified by theuser based on evaluation of the B-Mode image, by placing cursor linesoverlaid on the B-Mode image. A Fast Fourier Transform (FFT) of the RFdata can also be calculated and displayed. The acquisition of RF dataand the acquisition of B-Mode data can be interleaved so as to allow forthe display of information from both modes concurrently in real time.The acquisition of physiological signals such as the ECG signal can alsooccur concurrently with the acquisition of RF data. The ECG waveform canbe displayed while the RF data is acquired. The timing of theacquisition of RF data can be synchronized with user defined pointswithin the ECG waveform, thereby allowing for the RF data to bereferenced to specific times during a cardiac cycle. The RF data can bestored for processing and evaluation at a later time.

FIG. 17 shows a block diagram of the system 1600 further illustratingcomponents of an embodiment of the invention. The array transducer 1601is connected to the front end transformer 1702 via a cable 1619. Thecable 1619 comprises signal pathways from the elements of the arraytransducer 1601 to the front end transformers 1702. An exemplaryembodiment of the cable is described herein and comprises individualmicro-coax cables. In addition, connectors can be used on one or bothends of the cable 1619. In one aspect of the invention, a connector withpins equal to twice the number of elements can be used and an exemplaryconnector is described herein. For each element of the array transducer1601 a signal and a ground path can be used. In other embodiments of theinvention, the ground connection is shared for a grouping of elements. .Alternatively, the MUX/Front End Electronics 1702, 1703, 1704, 1708 canbe located inside the housing for the linear transducer array 1601

FIG. 17 provides representative details of the circuitry for fourelements of the array transducer 1601 as examples for the larger system1600 wherein there is a front end transformer 1702 and transmit outputstage 1703 for each element. For an embodiment with a 256 element arraytransducer 1601, there are 256 front end transformers 1702 and transmitoutput stages 1703. The front end transformers 1702 and transmit outputstages 1703 are more fully described below. During receive, theelectrical signal from an element of the array transducer 1601 passesthrough the front end transformer 1702 into the receive multiplexer1704. The receive multiplexer 1704 selects which element and front endtransformer are connected to the receive channel 1705. The receivechannel 1705 comprises a low noise amplifier and a time gain control,both more fully described below. The signal then passes from the receivechannel 1705 into the analog-to-digital conversion 1706 module where itis digitized. The digital received signal then passes into the receivebeamformer 1707, which is a digital beamformer. In block 1707, a delayprofile generated in the beamformer control is applied to the receivedsignal. The signal from the received beamformer 1707 travels into thesynthetic aperture memory 1710. The synthetic aperture memory adds thereceived data from two successive ultrasound lines. An ultrasound lineis considered to be the data resulting from returning ultrasound echoesthat is received after the transmission of an ultrasound pulse intotissue. Synthetic aperture imaging performs as one of ordinary skill inthe art would understand. In part, synthetic aperture imaging refers toa method of increasing the effective size of the transmit or receiveaperture. . For example, if there are 64 channels in the beamformer,during the reception of one line of ultrasound data, up to 64 transmitchannels and 64 receive channels can be used. Synthetic aperture imagingwill use two lines of ultrasound data, added together. The firstultrasound line can be acquired with a receive aperture which can spanelements 33 to 96. The second ultrasound line is received with anaperture segmented into two blocks, located at elements 1 to 32 and 97to 128. Both ultrasound lines use the same transmit aperture. When the 2ultrasound lines are summed, the resulting ultrasound line isessentially the same as that which would have been received had thereceive aperture consisted of 128 channels located at elements 1 to 128,provided that there is no appreciable motion of the tissue being imagedduring the time required to acquire the two lines of ultrasound data. Inthis instance two ultrasound lines were required rather than just one,so the frame rate is lowered by a factor of two. The two receiveapertures can be arranged in a different way, as long as together theyform a 128 element aperture. Alternatively, the transmit aperture sizecan be increased while keeping the receive aperture the same. More than2 ultrasound lines can be used to increase the aperture by more than afactor of two. The signal from the synthetic aperture memory 1710 isthen stored in the RF cine buffer 1713, which is a large memory thatsores many received RF lines, as controlled by the asynchronousprocessing control module 1714. The buffered receive signal is then readinto the signal processing unit 1715 at an appropriate rate. The signalprocessing unit 1715 may be implemented with a dedicated CPU on thebeamformer control board. The received signal passes from the signalprocessing unit 1715 to the computer unit 1717 where it is furtherprocessed according to the mode selected by the user. The processing ofthe received signal by the computer unit 1717 is generally of the typeknown to a person of ordinary skill in the art, with exceptions as notedherein.

In one embodiment, as shown in FIG. 17, the computer unit 1717 comprisessystem software configured to process signals according to the operationmode of the system. For example, the system software in the maincomputer unit 1717 may be configured to carry out B-Mode processes whichmay include, for example, preprocessing; persistence processing;cineloop image buffer; scan conversion; image pan; zoom andpostprocessing. The system software in the main computer unit 1717 mayalso be configured to carry out processes for color flow imaging (CFI),which may include, for example, threshold decision matrix; estimatefiltering; persistence and frame averaging; cineloop CFI image buffer;scan conversion; color maps and priority. The system software in themain computer unit 1717 may also be configured to carry out processesfor PW Doppler, which may include, for example spectral estimation(FFT); estimate filtering; cineloop spectral data buffer; spectraldisplay generation; postprocessing and dynamic range and audioprocessing.

The embodiment of the system of FIG. 17 is also comprised of a userinterface panel 1720. In this embodiment the user interface panel 1720is similar to the standard user interface found on most clinicalultrasound systems. For example, the B-Mode user interface may haveimage format controls that include image depth; image size; dual imageactivate; dual image left/right select; flip image left/right; flipimage up/down and zoom. Transmit controls may include transmit power(transmit amplitude); transmit focal zone location; number of transmitzones selection; transmit frequency and number of cycles. Imageoptimization controls may include; B-Mode Gain; TGC sliders;preprocessing; persistence; dynamic range; frame rate/resolution controland post-processing curves.

As another example of mode-dependent interface controls, a color flowimaging user interface may have image format controls that may includecolor flow mode select (e.g., color flow velocity, Power Doppler, TissueDoppler); trackball; steering angle; color box position/size select(after selection trackball is used to adjust position or size); presetrecall; preset menu and invert color map. Transmit controls may includetransmit power (transmit amplitude); transmit focal zone location andtransmit frequency. Image optimization controls may include; color flowgain; gate size; PRF (alters velocity scale); clutter filter select;frame rate/resolution control; preprocessing select; persistence;dynamic range (for Power Doppler only) and color map select.

Yet another example of a user interface is a PW Doppler user interfacewhich may have PW Doppler format controls that may include PW Dopplermode select; trackball; activate PW cursor (trackball is used to adjustsample volume position); sample volume size; Doppler steering angle;sweep speed; update (selects either simultaneous or interval updateimaging); audio volume control and flow vector angle. Transmit controlsmay include transmit power (transmit amplitude) and transmit frequency.Spectral Display optimization controls may include PW Doppler gain;spectral display size; PRF (alters velocity scale); clutter filterselect; preprocessing and dynamic range.

An exemplary M-Mode user interface may have image format controlsincluding M-Mode cursor activation; trackball (used to position cursor);strip size and sweep speed. Transmit controls may include transmit power(transmit amplitude); transmit focal zone location; transmit frequencyand number of cycles. Image optimization controls may include M-Modegain; preprocessing; dynamic range and post-processing.

An exemplary RF Mode user interface may have, for example, RF lineacquisition controls that may include RF line position; RF gate; numberof RF lines acquired; RF region activate; RF region location; RF regionsize; number of RF lines in region; averaging; and B-Mode interleavedisable. Transmit controls may include transmit power (transmitamplitude); transmit focal zone location; transmit f-number; transmitfrequency; number of cycles; acquisition PRF and steering angle. Receiveprocessing controls may include RF Mode gain; filter type, order; windowtype and number of lines averaged.

The digital samples of the received signal are processed at a rate whichis generally different from the rate at which the data is acquired. Suchprocessing is referred to herein as “asynchronous signal processing.”The processing rate is the rate at which data is displayed, typicallyabout 30 frames per second (fps.) As one would recognize, however, thedata can be displayed at a rate up to the acquisition rate or can bedisplayed at less than about 30 fps. The data can be acquired at muchfaster frame rates, in certain embodiments of the invention at about 300frames per second, or at a speed necessary to acquire the diagnosticinformation desired. For example, image date of a rapidly movinganatomical structures such as a heart valve can be acquired using afaster frame rate and then can be displayed at a slower frame rate. Dataacquisition rates can be less than 30 fps, 30 fps, or more than 30 fps.For example, data acquisition rates can be 50, 100, 200, or 300 or morefps.

The display rate can be set such that it does not exceed that which thehuman eye can process. Some of the frames which can be acquired can beskipped during display, although all of the data from the receivebeamformer output is stored in an RF data buffer such as the RF cinebuffer 1713. The data is sometimes referred to as RF data or by thesampling method used to acquire the data, (for instance in the case ofquadrature sampling, the data can also be referred to as basebandquadrature data). The quadrature or RF data is processed prior todisplay. The processing may be computationally intensive, so there areadvantages to reducing the amount of processing used, which isaccomplished by processing only the frames which are to be displayed atthe display rate, not the acquisition rate. The frames that were skippedover during display can be viewed when live imaging stops or the systemis “frozen.” The frames in the RF buffer 1713 can be retrieved,processed, and played back at a slower rate, e.g., if the acquisitionrate is 300 frames per second, the play back of every frame at 30 framesper second would be 10 times slower than normal, but would allow theoperator to view rapid changes in the image. The playback feature isusually referred to as the “Cineloop” feature by persons of ordinaryskill in the art. Images can be played back at various rates, or frameby frame, backwards and forwards.

The system 1600 shown in FIG. 17 can also comprise various items whichone of ordinary skill in the art would recognize as being desirable forthe function of the system, such as clocks 1712, memory, sound card andspeakers, video card and display, etc. and other fimctional blocks asshown in FIG. 17.

FIGS. 18 a and 18 b provide additional detail of an embodiment of theMUX/Front End Electronics 1702, 1703, 1704, 1708 and the receivebeamformer 1707 and transmit beam former 1709 functions according to anembodiment of the present invention. In the embodiment shown in FIG. 18a, a channel, for instance a receive channel, can be connected to a nodeand that node is connected to, for example, four (4) elements of thearray transducer 1601 through a switching circuit, or multiplexingcircuit, as shown in FIG. 18 a. For instance, channel 1 1801 may beswitchably connected to elements numbered 1, 65, 129, and 193 in FIG. 18a so that only one of those four elements are connected to channel 11801 at any given time. This, in essence, is the performance of themultiplexing function of the MUX/Front End Electronics 1702, 1703, 1704,1708 during the receive cycle of the system 1600. The assignment of fourswitchably connected elements to a channel is done such that contiguouselements of any given subset of elements can comprise the activeaperture. For example, if the array transducer were comprised of 256elements, then 64 or less elements can form the subset that comprisesthe active aperture.

The multiplexing of the elements of the array transducer 1601 for thereceive cycle can be carried out by a RX switch 1817 as shown in anexemplary diagram (FIG. 18 b) of the front end 1802. A control signal1818 from the beamformer control 1711 determines which RX switch 1817 isactivated, thereby connecting the chosen element of the four (4)available elements for that module 1802 to the receive channel. As oneskilled in the art would appreciate, the multiplexing scheme illustratedin FIGS. 18 a and 18 b can be applied to transducers of varying numbersof elements (other than 256 elements) and of varying maximum activeaperture sizes (other than up to 64 elements).

The exemplary front end 1816 shown in FIG. 18 b also comprises thetransformer 1819 and pulser 1820, which are described in more detailbelow. In one aspect, the front end 1816 provides isolation of thereceive channel from the transmit waveform, discussed previously herein.

The received signal from the selected array transducer element passesinto the low noise amplifier (LNA) 1804. From the LNA 1804, the thenamplified signal passes into time gain control (TGC) 1805. Since elapsedtime is proportional to the depth of the received reflected signals,this is also referred to as a depth dependent gain control. In anultrasound system, as time goes by from the transmission of anultrasound wave, the signal passes deeper into the tissue and isincreasingly attenuated; the reflected signal also suffers thisattenuation. The TGC 1805 amplifies the received signal according to atime varying function in order to compensate for this attenuation. Thefactors which can be used to determine the time varying TGC gain aretime of flight, tissue characteristics of the subject or subject tissueunder study, and the application (e.g. imaging modality). The user mayalso specify gain as a function of depth by adjusting TGC controls onthe user interface panel 1607. Embodiments may use, for example, anAnalog Devices (Norwood, Mass.) AD8332 or similar device to perform theLNA 1804 and TGC 1805 functions. From the TGC 1805, the receive signalpasses into the receive beamformer 1803 where it is sampled by asampler, in this embodiment, the analog-to-digital converters 1807 and1808. In other embodiments according to the invention only oneanalog-to-digital converter is used if sampling is done at a rategreater than the Nyquist rate; for instance at 2 or 3 times the Nyquistrate, where the Nyquist rate involves sampling the ultrasound signalsfrom the individual elements at a rate which is at least twice as highas the highest frequency in the signal.

In other embodiments of the invention, quadrature sampling is employedand two analog-to-digital converters are used, namely the “I’ and the“Q” sampler. In the exemplary embodiment of the receive beamformer 1803,the receive signal is digitized in blocks 1807 and 1808 using quadraturesampling analog-to-digital converters (ADC); two ADCs are required perchannel, with sampling clocks shifted 90° out of phase. The sample rateused can be the center frequency of the receive signal. For comparison,direct sampling would use a sampling rate in theory of at least twicethe highest frequency component in the receive signal, but practicallyspeaking at least three times the sampling rate is preferred. Directsampling would use one ADC per channel.

Once sampled, the now digitized received signal passes into a FieldProgrammable Gate Array (FPGA) in which various functions associatedwith receive beamforming are implemented. Within the FPGA, the digitizedreceived signal can undergo a correction for the DC offset of the ADC.This is implemented by the subtraction of a value equal to the measuredDC offset at the ADC output. Each ADC may have a different DC offsetcorrection value. The DC offset may be determined by averaging a numberof digital samples appearing at the output of the ADC with no signalpresent at the receive channel input, for example, during a calibrationperiod at system start up. The digitized signal next passes into a FIFObuffer 1822 where each sample is stored for an appropriate duration sothat the appropriate delay profile can be implemented. The delay can beimplemented in both coarse and fine manners. A coarse delay can beimplemented by shifting the signal by one or more sample points toobtain the desired delay. For instance, if the desired delay is onesample period, then shifting by one sample in the appropriate directionprovides a signal with the appropriate delay. However, if a delay of avalue not equal to the sample period is desired, a fine delay can beimplemented using an interpolation filter 1809.

From the FIFO buffer 1822, the digitized received signal passes into theinterpolation filter 1809 for the calculation of any fine delay. Theinterpolation filter 1809 is used in a system where the sample period isgreater than the appropriate fine delay resolution. For instance, if thesample rate is the center frequency of the ultrasound signal and is 50MHz, the sample rate is one sample every 20 nanoseconds. However, adelay resolution of 1.25 nanoseconds ( 1/16 of 20 nanoseconds) is usedin certain embodiments to provide the desired image quality, thoughother delay resolutions are contemplated within the scope of thisinvention. The interpolation filter 1809 is used to calculate a valuefor the signal at points in time other than the sampled point. Theinterpolation filter 1809 is applied to the in-phase and quadratureportions of the sampled signal. Embodiments of the interpolation filter1809 comprise a finite impulse response (FIR) filter. The coefficientsof each filter can be updated dynamically by the beamformer controlmodule based on the time of flight, sample by sample. After processingby the interpolation filter, a phase rotation can be applied by amultiplier 1811 multiplying the in-phase and quadrature components bythe appropriate coefficients. The phase rotation is used to incorporateinto the interpolated sample the correct phase relative to the ADCsample frequency. The RX controller 1810 controls the FIFO modules andthe interpolation filters. The receive delay is updated dynamically, sothe interpolation filter coefficients at each channel need to change atcertain intervals. The delay implemented by the FIFO also needs tochange at certain intervals. Also, the receive aperture size is adjusteddynamically, so each channel becomes active at a specific time duringthe reception of the ultrasound signal; a channel is activated bymultiplying by 1 instead of 0 at the “multiply” module 1811. Themultiply module 1811 can also apply a “weight” which is a value between0 and 1, independently to each channel in the receive aperture. Thisprocess, which is known as apodization, is known to one skilled in theart. The value by which the interpolated sample is multiplied by mayvary with time, so as to implement an apodized receive aperture whichexpands dynamically during the reception of the ultrasound signal.

FIG. 18 c is an exemplary embodiment of a receive controller (RXcontroller) in an embodiment according to the present invention. TheReceive Controller 1810 is used to program the correct delay profile,aperture size and receive apodization data into the processing block1809 which implements the interpolation and phase rotation andapodization. The Receive Controller 1810 of FIG. 18 c sets the initialparameters (Initial Coarse Delay, Initial Phase) once per start-of-line(SOL) trigger and sets the dynamic parameters (Dynamic Focus, DynamicApodization) once per receive clock (RXCLK) period. The initial receivedelay profile is stored in RX Initial Aperture Memory 1822. The dynamicreceive delay profile is stored in the RX Dynamic Aperture Memory 1824.The delay profile is loaded into the RXBF Buffer 1826 via the 64:16Crosspoint Switch 1828 before the SOL trigger. The crosspoint switch1828 selects 16 of the 64 aperture channel configurations. These areused to program the 16 receive channels that are on a single Channelboard.

The configuration for each receive line is stored in the Line Memory1830. Each line configuration in the Line Memory 1830 contains theAperture Select Index, the Mode Select, and the Aperture Enable. TheAperture Select index is used to determine the Aperture to Channelmapping. The Mode Select is used to access multiple delay profiles. TheAperture Enable index controls the initial aperture size. The apertureselect look-up table (AP_SEL LUT) 1832 is a method to reduce the numberof possible configurations and therefore number of bits required tostore in the line memory. The AP_SEL LUT 1832 is re-programmable.

The Memory Control 1834 is a state machine that decodes the lineconfiguration. The state machine is configured by the Control and Statusmemory 1836. It is configured differently for different modes (e.g.B-Mode, Color Flow Mode, PW Doppler Mode, etc.). The Memory Control 1834controls the loading of the aperture memory into the RXBF Buffer 1826and generates the SOL_delayed and FIFO_WEN signals. The pulseSOL_delayed is used to transfer the initial delay parameters into the RXPhase Rotation and RX Apodization block 1809 in a single RXCLK period.The dynamic receive parameters are then transferred in each subsequentRXCLK period. The FIFO_WEN signal starts the receive ADC dataacquisition into the FIFO for the RX interpolation filter.

The Control and Status Memory 1836 also contains common parameters suchas the Receive Length. The Receive Length parameter determines how manyreceive samples to collect for each line.

It is to be appreciated that increasing the number of receive channelsallows for larger receive apertures, which can benefit deep imaging byimproving lateral resolution and penetration. The synthetic aperturemode allows for apertures greater than 64 to be used, but at the expenseof a reduction in frame rate. With an increase in the number ofreceivechannels, this can be done without a frame rate penalty.

In one embodiment according to the present invention, the receivebeamformer 1803 allows for multi-line beamforming. Multi-linebeamforming allows for higher frame rates by processing multiple receivelines in parallel. Frame rate increases by a factor equal to the numberof parallel receive lines. Since beamforming occurs simultaneously formultiple receive apertures, higher data processing rates through theinterpolation filters 1809 are used. The amount of data transferred fromthe receive beamformer to a host CPU would increases by a factor equalto the number of parallel receive lines. The transmit beam is broadenedso that it overlaps the multiple receive lines.

The signal from each receive beamformer 1803 is then summed by summers1815. The summed signal represents a received signal at a given timethat is reflected from a given depth. The summed received signal is thenrouted through modules described earlier and shown in FIG. 17, to theappropriate processing module for the mode of operation selected by theuser.

During the transmit operation cycle of the system 1600, selectedtransmit output stages are connected to the transmit channel in order toform the active aperture. In this aspect, the multiplexing is done priorto the transmit output stage. For example, as previously described,transmit channel 1 1801 can be switchably connected to the transmitoutput stages corresponding to elements numbered 1, 65, 129, and 193 inFIGS. 18 a and 18 b so that only one of those four transmit outputstages are connected to transmit channel 1 1801 at any given time. Itcan also be seen in FIGS. 18 a and 18 b that transmit channel 2 can beswitchably connected to the transmit output stages corresponding toelements 2, 66, 130 and 194, and so on. This is the performance of themultiplexing function of the MUX/Front End Electronics 1702, 1703, 1704,1708 during the transmit cycle of the system.

Referring to FIG. 20, the transmit signal which is multiplexed is thepair of signals designated by TXA 2002 and TXB 2004, which drive thegates of the transmit pulser MOSFETs QTDN 2006 and QTDP 2008 as shown inFIG. 20. These signals 2002, 2004 are unipolar signals of a sufficientlylow level so that multiplexing by MOSFET type switches can be used. Theassignment of four switchably connected transmit output stages to atransmit channel is done such that contiguous elements of any givensubset of elements can comprise the active transmit aperture. Forexample, in an array transducer comprised of 256 elements, 64 or lesselements can form the subset that comprises the active transmitaperture.

Optionally, the transmit multiplexing can be done after the transmitoutput stage using multiplexing circuitry able to accommodate a highervoltage bipolar signal.

Referring back to FIGS. 18 a-18 d, the transmit beamformer 1812generates the transmit waveform with the specified delay present in thewaveform in that the waveform is not sent until the appropriate time perthe delay profile. The transmit waveform can be a low voltage signal,including a digital signal. Optionally the transmit waveform can be ahigh voltage signal used by the array transducer to convert electricalenergy to ultrasound energy. The operation of the transformer 1819 andpulser 1820 are described in greater detail below.

During the process oftransmit beamforming, one or more of each of thetransmit channels within the active transmit aperture can produce atransmit waveform which can be delayed relative to a reference controlsignal. The number of transmit channels determines the maximum transmitaperture size. The benefit of increasing the number of transmit channelsis improved lateral resolution and penetration for deep imaging. Invarious embodiments, the array transducer has 64 transmit channels ormay have 96 or 128 transmit channels. The delays can vary from channelto channel, and collectively the delays are referred to as the transmitdelay profile. Transmit beamforming may also include the application ofa weighting function to the transmit waveforms, a process known to oneof ordinary skill in the art as “apodization.” Transmit apodization usesindependent control of the amplitude of the transmitted waveform at eachchannel. The benefit to image quality is improved contrast resolutiondue to a reduction in spurious lobes in the receive beam profile, whichcan be either side lobes or grating lobes. Each transmitter output stagecan have an independently controlled supply voltage, and controlhardware.

Transmit waveshaping involves the generation of arbitrary waveforms asthe transmit signal, i.e., the modulation of amplitude and phase withinthe transmit waveform. The benefit is an improvement to axial resolutionthrough shaping of the transmit signal spectrum. Techniques such ascoded excitation can be used to improve penetration without loss ofaxial resolution.

The transmit beamformer 1812 described herein may be implemented in oneembodiment with an FPGA device. A typical implementation of a transmitbeamformer 1812 which provides a delay resolution of, for example, 1/16the transmit clock period may require a clock which is 16 times thetransmit clock frequency. For the frequency range of the systemdescribed here, this would imply a maximum clock frequency of 16 times50 MHz, or 800 MHz, and a typical FPGA device may not support clockfrequencies at that rate. However, the transmit beamformer 1812implementation described below uses a clock frequency within the FPGA ofonly eight (8) times the transmit clock frequency.

Each channel of the transmit beamformer is comprised of a TX controller1814 and a Tx pulse generator 1813. The TX controller 1814 uses aparameter called, for example, an ultrasound line number (also known asa ray number), to select the active transmit aperture through theappropriate configuration of the transmit multiplexer. The ray numbervalue identifies the origin of the ultrasound scan line with respect tothe physical array. Based on the ray number, a delay value is assignedto each transmit channel in the active transmit aperture. The TX pulsegenerator 1813 generates a transmit waveform for each transmit channelusing waveform parameters and control signals as described herein.

FIG. 18 d is an illustration of an exemplary transmit controller (TXcontroller) in an embodiment according to the present invention. Thetransmit controller 1814 is used to program the TX pulse generator 1813with the correct delay profile (coarse delay and fine delay for eachchannel) and transmit waveform for each line. It re-programs the TXpulse generator 1813 before each line. The sequence of lines is used toproduce a 2-D image. Each line requires a certain subset of the arrayelements to be used to form the transmit aperture. Each array elementwithin the aperture must be connected to a channel in the TX pulsegenerator 1813, and the transmit channels must be configured to producethe desired transmit waveforms with delays according to the desiredtransmit delay profile.

The delay profile and transmit waveform for the entire aperture isstored in the TX Aperture Memory 1838. Multiple delay profiles can bestored in the TX Aperture Memory 1838. Multiple delay profiles arerequired for B-Mode imaging in which multiple focal zones are used, andPW Doppler and Color Flow Imaging modes in which the Doppler mode focaldepth and transmit waveforms are different than those used for B-Mode.In this exemplary embodiment, the TX Aperture Memory 1838 contains delayprofile and transmit pulse wave shape data for a 64 channel aperture. Oneach Channel Board there are 16 transmit channels, each of which can beconnected to one of four different array elements through a transmitoutput stage. A 64:16 crosspoint switch 1840 is used to route thecorrect transmit waveform data sets to each of the 16 channels. Thecontrol of the other 48 channels is implemented on the other 3 channelboards. The TXBF buffer 1842 temporarily stores the TX pulse generatordata before the start of line (SOL) trigger. The TX_TRG trigger movesthe data from the TXBF Buffer 1842 into the TX Pulse generator 1813 inone TXCLK period.

The configuration for each transmit line is stored in the Line Memory1844. Each line configuration in the Line Memory 1844 contains thefollowing information: Aperture Select Index, Mode Select, ApertureEnable Index, and Element Select Index. The Aperture Select index isused to determine the Aperture to Channel mapping. The Mode Select isused to access multiple delay profiles. The Aperture Enable indexcontrols the aperture size. The Element Select index controls whichelement is active in the case that there are more array elements thantransmit channels or receive channels. The indexing of the ApertureSelect, Aperture Enable and Element Select look-up tables (AP_SEL LUT1846, AP_EN LUT 1848, ES LUT 1850) is a method to reduce the number ofpossible configurations and therefore number of bits required to storein the line memory 1844. The look-up tables are all re-programmable.

The Control and Status memory 1852 contains common parameters such asthe number of transmit cycles (TX Cycles), the number of lines in theframe, and also configures the state machine in the Memory Control block1854. Memory Control 1854 is a state machine that decodes the ApertureSelect, Aperture Enable and Element Select line information.

Referring to FIG. 20, it can be seen that the transmit waveform isactually two signals, referred to as the “A” and “B” signals, one ofwhich is applied to the gate of pulser drive MOSFET QTDN 62006 and theother applied to the gate of pulser drive MOSFET QTDP 2008. The “B”signal can be identical to the “A” signal except that it is delayed by ½the period of the transmit clock. The delay applied to each transmitwaveform is divided into two components, the “coarse delay” and the“fine delay”. The coarse delay can be in units of ½ of the transmitfrequency period, and the fine delay can be in units of 1/16 thetransmit frequency period, though other units of fine delay arecontemplated within the scope of this invention. Other aspects of thetransmit waveform which can be adjusted are the transmit centerfrequency, pulse width, number of cycles and the “dead time”. The “deadtime” is the time interval following the first half cycle of the outputpulse in which neither of the two output stage MOSFETs, QTDN 2006 andQTDP 2008, are turned on. Alteration of the transmit center frequency,pulse width and dead time may be used to alter the frequency content ofthe final transmit signal to the transducer element.

Referring now to FIGS. 22-22C, in an embodiment according to the presentinvention, one transmit pulse generation circuit 2200 is used for eachtransmit beamformer channel. A 16 bit A waveshape word 2202 is used toencode the fine delay, pulse width and dead time for the A signal. A 16bit B waveshape word 2203 is used to encode the fine delay, pulse widthand dead time for the B signal. The waveshape words 2202, 2203 can bestored in memory within, for example, a FPGA. The frequency of thetransmit output signal is determined by the frequency of the transmitclock. The control inputs come from the transmit controller 1814, whichcan be implemented within the FPGA. These can be the pulse count 2204,the TXTRG 2206, and various clocks, as described below, and shown inFIGS. 22-22C .

Transmit pulse generation begins when a TXTRG pulse 2206 is receivedfrom the channel control board 1814. The TXTRG signal 2206 is sent tothe transmit beamformer channels, and is the signal which the transmitbeamformer delays are referenced to. The TXTRG pulse 2206 begins thecounting of ½ intervals of the transmit frequency clock cycle denoted byTXCLK×2 2246. The current hardware implementation uses a clock of 2times the transmit clock. The coarse delay 2210 is implemented by aCoarse Delay counter 2248 which is clocked by a clock, TXCLK×2 2246. Thesignal TXTRG 2206 causes the count to begin.

A COARSE DONE signal 2208 is generated when the number of clock cyclesof TXCLK×2 2246 has reached the coarse delay input variable value 2210.The COARSE DONE signal 2208 enables the byte select circuit composed ofmultiplexers 2250 and 2252, Pulse Inversion select Circuit composed ofmultiplexers 2254 and 2256, and the 8:1 parallel-to-serial circuits 2212and 2213. The 16 bit waveshape words 2202 and 2203 are transferred into16 bit registers 2216 and 2217. The output of the A waveshape register2216 is composed of the Partial Waveshapes: Partial_Waveshape_A(7:0)2260 and Partial_Waveshape_A(15:8) 2261. Partial_Waveshape_A(7:0) 2260is transferred to the either 8:1 parallel-to-serial circuit 2212 or 8:1parallel-to-serial circuit 2213 through the Pulse Inversion Circuitcomposed of multiplexers 2254 and 2256. Following the transfer ofPartial_Waveshape_A(7:0) 2260, Partial_Waveshape-A(15:8) 2261 istransferred to the either 8:1 parallel-to-serial circuit 2212 or 8:1parallel-to-serial circuit 2213 through the Pulse Inversion Circuitcomposed of multiplexers 2254 and 2256. The Byte Select signal 2214controls which of Partial_Waveshape A(7:0) 2260 orPartial_Waveshape_A(15:8) 2261 is multiplexed through to the PulseInversion Circuit. In this way, the full 16 bits of Waveshape_A 2202 istransferred to the 8:1 parallel-to-serial circuits for serializationinto a one bit data stream.

As can be seen from FIG. 22, the transfer of the Waveshape_B 2203 isdone in a similar manner.

The 8:1 parallel-to-serial circuit 2212 and 2213 have double data rate(DDR) outputs. COARSE DONE 2208 begins the count of the number of outputpulses. When the pulse number counter finishes counting the number ofpulses, the Enable signal 224 goes low causing the registers 2216 and2217 to stop outputting the Partial Waveshapes. The 16-bit waveshape ofthe “A” phase 2202 is converted to 1 serial bit in two TXCLK×2 2246cycles. The 16-bit waveshape of the “B” phase 2203 is also converted to1 serial bit in two TXCLK×2 2246 cycles. Pulse inversion may be achievedby swapping the “A” and “B” phases before the signals are sent to theparallel-to-serial circuits. The signal swap occurs if the PulseInversion signal 2258 is enabled on the Pulse Inversion MUX circuit 2254and 2256.

The 8:1 parallel-to-serial circuit with double data rate (DDR) output isclocked with TXCLK×8 2266 which is at a frequency of 8 times thetransmit clock. With DDR output, the waveshape is shifted out at a rateof 16 times the transmit clock frequency. The signals from 8:1parallel-to-serial circuit 2212 or 8:1 parallel-to-serial circuit 2213are transferred out of the FPGA using the LVDS standard before it isre-synchronized by clock TXCLK×16 2236.

The “A” phase signal is re-synchronized by a low jitter positive emittercoupled logic (PECL) flip-flop 2234 and a low jitter clock, TXCLK×162236, at 16 times the transmit frequency. This can eliminate jitteradded by the circuit inside the FPGA. The “B” phase signal is alsore-synchronized by flip-flop 2235.

Both the “A” and “B” signals go to respective driver circuits 2238, 2240to increase their current drive capability. The output of the driversbecome signals TXB 2004 and TXA 2002 and connect to the transmitmultiplexers in the front end circuit 2000.

Re-sending of the waveshape data 2202 and 2203 continues until the pulsenumber counter 2242 has reached the number specified by the pulse countinput variable 2204 and the enable signal 2244 changes state.

The 16 bit word which constitutes Waveshape A 2202 may change from onetransmit cycle to the next. The same applies to Waveshape_B 2203. Thisallows for the generation of transmit waveforms with arbitrarilyspecified pulse widths from one cycle to the next. Waveshape_A 2202 andWaveshape_B 2203 are specified independently. For example, either odd oreven transmit waveforms may be generated.

FIGS. 22A-22C illustrate how the waveshape data can be used to changethe fine delay, pulse width and dead time for the “A” and “B” signals.In this example, the “B” output is identical to the “A” output except itis delayed by ½ of the transmit frequency period. FIG. 22C illustratesthat arbitrary waveforms can be generated in the “A” phase and the “B”phase. Ny Waveshape_A may be different from the one preceding it, andany Waveshape_B may be different from one preceding it. In the examplein FIG. 22C, the 16 bit waveforms used for Waveshape_A1(15:0), WaveshapeA2(15:0)and Waveshape_A3(15:0) are different from one another. In thisexample, the Waveshape_B(15:0) is repeated twice, but it would bepossible to specify that a Waveshape-B be different from the precedingWaveshape_B. The A and B waveforms are independent and can be used toimplement transmit waveforms used for coded excitation methods, forexample in applications involving contrast agent imaging and non-linearimaging.

The TXPower signal (shown as “TX High Voltage” in FIG. 18 b) can controlthe amplitude of the output of the transmit pulser. As shown in thisimplementation, TXPower is common to all transmit channels. Optionally,the amplitude of the output pulse of each transmit channel can becontrolled individually.

FIG. 19 is a system signal processing block diagram illustrating anexemplary beamformer control board 1900. The beamformer control board1900 is an exemplary embodiment of the beamformer control and signalprocessing block 1716. The design and operation of the beamformercontrol board 1900 is generally known to one of ordinary skill in theart. Embodiments of the exemplarily system can have the capability toacquire, process and display physiological signal sources 1901 of one ormore of, for example, ECG, respiration, body temperature of the subject,or blood pressure. The physiological signal acquisition block 1902 cancontain signal acquisition modules that can acquire those types ofphysiological signals.

The data transfer to computer unit 1903 transfers data from thebeamformer control board 1900 to the computer unit 1905. Embodiments canuse a PCI express bus 1904, as is known in the art, for this transfer,or similar buses.

FIG. 20 is an exemplary schematic 2000 of the front end circuittransformer 1702, transmit output stage 1703 and the receive MUX 1704and the transmit MUX 1708. Other exemplary front end circuits can alsobe used with the described system. For example, front end circuits asdescribed in U.S. Pat. No. 6,083,164, entitled “Ultrasound Front-EndCircuit Combining the Transmitter and Automatic Transmit/ReceiveSwitch,” which is fully incorporated herein by reference and made a parthereof, can be used. The exemplary circuit 2000 depicted in FIG. 20provides the multiplexing function of connecting an element to thereceive channel if that element is part of the active aperture. Thefront end circuit also provides isolation of the receive channel fromthe transmit channel, as described herein. The transmit output stagereceives a transmit waveform from the transmit pulse generator 1813 andin turn combines the transmit pulse information with transmit highvoltage to create a high voltage waveform at an element which is part ofthe active transmit aperture.

In the exemplary schematic shown in FIG. 20, transmit pulsing iseffected by D1 2010, D2 2012, QTDP 2008, QTDN 2006, QTXMUXP 2014,QTXMUXN 2016 and T1 2018. During transmit, the transmit output stagewhich is included in the active transmit aperture is connected byturning on QTXMuxP 2014 and QTXMUXN 2016 to allow the gate drivesignals, TXA 2002 and TXB 2004, to reach QTDN 2006 and QTDP 2008. Duringtransmit pulsing, either QTDN 2006 or QTDP 2008 are turned onseparately, with timing as required to produce the intended transmitwaveform. The pulser output appears on the left end of the transformersecondary, LTXS 2038, while the right end is clamped near 0 V by D1 2010and D2 2012, which can be, for example, ordinary fast silicon switchingdiodes. During active pulsing, the receive multiplexing switch SW1 2020can also be turned off to provide additional isolation. The amplitude ofthe output of the transmit pulser is determined by the transmit supplyvoltage applied to the center tap of the primary of T1 2018 through R12022. Two voltage supplies are available, V1 2024 and V2 2026, where V12024 is larger than V2 2026. They are connected to a common node at theR1 2022 as shown through FET switches QLSH 2028, QLSL 2030 and diode D32032. One or the other of the supply voltages is selected by turning oneither QLSH 2028 or QLSL 2030 using control signals V1 NE 2034 and V2 NE2036. Diode D3 2032 helps prevent current from flowing from V1 2024 toV2 2026 when V1 2024 is connected to R1 2022. This configuration allowsfor rapid switching of the transmit supply voltage between two levels,since it avoids the requirement to charge or discharge the supplyvoltage as held on voltage storage capacitors C4 and C5.

Receive switching is effected by QTDP 2008, QTDN 2006, QLSH 2028, QLSL2030, and SW1 2020. SW1 2020 is a receive multiplexing switch which canbe a single pole single throw (SPST) or a single pole double throw(SPDT) switch of a type such as a GaAs PHEMT (gallium arsenidepseudomorphic high electron mobility transistor). Alternatively, thereceive multiplexing switch may be implemented with other types of fieldeffect transistors or bipolar transistors. If SW1 2020 is a SPDT switchit is configured as shown in FIG. 20, where one terminal is connected toa terminating resistor and the other is connected to the receive channelinput. If SW1 2020 is a SPST switch, the terminal connected to theterminating resistor and the terminating resistor is deleted.

During receive intervals, the receive multiplexing switch is configuredsuch that there is a connection between the array element and thereceive channel. The pulser drive MOSFETs, QTDN 2006 and QTDP 2008, areboth turned on during receive, while QLSH 2028, QLSL 2030, QTXMUXN 2016and QTXMUXP 2014 are held off. This causes LTXS 2038 to present mainlyits leakage inductance as an impedance in series with the receivesignal. For received signals too small to forward bias D1 2010 or D22012, these diodes present high shunt impedance, dominated by theirjunction capacitance. L1 2040 and the leakage inductance LTXS 2038 areused to level the receive mode input impedance, compensating for thejunction capacitance of D1 2010, D2 2012 and the capacitance of theganged switches forming the receive multiplexer In an alternativeimplementation of the front end circuit, and as shown in FIG. 21, signalRXCLMP is eliminated and its' function performed by TXA and TXB. Thetransmit function on this circuit is identical to the circuit of FIG. 20with QTXMUXN and QTXMUXP gating signals TxDriveN and TXDriveP. Inreceive mode QTXMUXN and QTXMUXP are off thus blocking signals TXA andTXB. Resistors R8 and R9 shunt QTXMUXN and QTXMUXP so that when TXA andTXB are driven high for the duration of receive mode the voltage on thegates of QTDN and QTDP increases slowly resulting in gentle activationof these MOSFET switches. The gentle activation of QTDN and QTDP forreceive mode is controlled by signal RXCLMP in the circuit of FIG. 20.In FIG. 21, resistors R5 and R6 pull the voltage on the gates of QTDNand QTDP to ground when transmit multiplexing switches are turned offafter a transmit operation.

The pulser employs a center-tapped transformer and NMOS FETs, togetherwith a switch-selectable level supply, to generate nominally squarepulses. In order to control the delivered spectrum when connected to thetransducer element thru a controlled impedance coax cable, it employsseries and shunt resistances. These serve to reduce the time-variationof source impedance during operation of the pulser and provide backtermination of the transducer during the interval immediately followingtransmit pulses. Not shown in the schematic is the drive circuit for thefinal stage MOSFETs. This circuit, (which is on the far side of amultiplexer as describe below), may be either a discrete switchingMOSFET pulse amplifier or a collection of CMOS buffers sufficient toprovide the required drive.

The transformer needed for the pulser is built as windings printed onthe PCB augmented by small ferrite slabs fastened onto both sides of thePCB, around the windings. This technique is amenable to automatedassembly provided the ferrite slabs can be packaged appropriately.

EXAMPLES

The following examples are put forth so as to provide those of ordinaryskill in the art with a complete disclosure and description of how thearticles, devices and/or methods claimed herein are made and evaluated,and are intended to be purely exemplary of the invention and are notintended to limit the scope of what the inventors regard as theirinvention. Efforts have been made to ensure accuracy with respect tonumbers (e.g., amounts, temperature, etc.), but some errors anddeviations should be accounted for.

Example 1

FIG. 23 is a block diagram showing exemplary system according to anembodiment of the present invention. The exemplary system 2300 isinterfaced with a linear array 2302 having, for example, up to 256elements. A bundle of micro coax cables 2304 provides transmission ofthe signals between the array 2302 and the processing unit 2306. Theexemplary system funrther comprises a processing unit.

The processing unit 2306 is partitioned into two major subsystems. Thefirst is the front end 2308, which includes the beamformer, the frontend electronics, the beamformer controller and the signal processingmodule. The second is the computer unit 2310, or back end. The front endsubsystem 2308, is concerned with transmit signal generation, receivesignal acquisition, and signal processing. The back end 2310, which canbe an off-the-shelf PC motherboard, is concerned with system control,signal and image processing, image display, data management, and theuser interface. Data can be transferred between the front and back endsub-systems by, for example, a PCI express bus, as is known in the artto one of ordinary skill.

The module which processes the receive signals is the receivebeamformer, as previously described herein. The subsystem whichgenerates the transmit signals is the transmit beamformer, also aspreviously described herein. Each channel of the transmit and receivebeamformers is connected to a separate element in the array 2302. Byaltering the delay and amplitude of the individual transmit or receivesignals at each element, the beamformer is able to adjust the focaldepth, aperture size and aperture window as a function of depth. Theexemplary system of FIG. 23 may support one or more various modes ofultrasound operation as are known in the art to one of ordinary skill.These modes are listed in Table 2, below: TABLE 2 Modes Supported B-ModeM-Mode PW Doppler Color Flow (Velocity) Doppler Power Doppler TissueDoppler 2nd Harmonic Triplex EKV ECG triggered imaging 3-D imaging 3-Dreal-time (4 Hz) RF Mode Anatomical M-ModeSystem Specifications

Exemplary specifications of the system shown in FIG. 23 may include, forexample, those specifications listed in Tables 3, below: TABLE 3 SystemSpecifications Number of transducer elements supported Up to 256Transmit channels (active aperture) 64 Receive channels 64 Transducerssupported Linear, curved linear Center frequency range 15 to 55 MHz Dataacquisition method Quadrature sampling BF sampling frequency range 15 to62 MHz Receive BF fine delay implementation Interpolation filter Receivedelay resolution T/16 ADC number of bits 10 Transmit delay resolutionT/16 TGC yes Synthetic Aperture yes Maximum transmit voltage 80 VppTransmit power control yes Multiple Transmit focal zones yes Transmitcycle adjustment 1-32 B-mode frame rate max 200  CFI frame rate max 160 PW Doppler maximum PRF 150 KHz CFI maximum PRF  75 KHz Doppler beamsteering yes Cine buffer size 300 frames Physiological signalacquisition yes Transducer connectors One or moreSystem Cart

The system or portions thereof may be housed in a portable configurationsuch as, for example, a cart, including beamformer electronics 2316, acomputer unit 2310, and a power supply unit 2312. The user interfaceincludes an integrated keyboard 2318 with custom controls, trackball,monitor, speakers, and DVD drive. The front panel 2320 of the cart hasconnectors 2322 for connecting an array-based transducer 2302 and mousephysiological information such as ECG, blood pressure, and temperature.The rear peripheral panel 2314 of the cart allows the connection ofvarious peripheral devices such as remote monitor, footswitch, andnetwork 2324. The cart has a system of cooling fans 2326, air guides,and air vents to control the heat of the various electronics.

In one embodiment the computer unit 2310 may be an off-the-shelf Intelarchitecture processor running an operating system such as, for example,Microsoft Windows XP. The computer unit 2310 may be comprised of, forexample, an Intel 3 GHz CPU (Xeon Dual Processor or P4 withHyperthreading); 2 GB DDR memory; PCI Express ×4 with cable connector;100 Mbps Ethernet; USB 2.0; Graphics controller capable of 1024×768×32bpp @ 100 Hz; Audio output (stereo); 2×120 GB 7200 RPM Hard disk drives(one for O/S+software; one for user data) and 300 W ATX power supplywith power-factor correction

In one embodiment the power supply unit 2312 may be comprised of thefollowing: a universal AC line input (100, 120, 220-240 VAC, 50 or 60Hz), where the AC input is provided by a detachable cable that connectsto a system AC input terminal block and has AC distribution using IECterminal blocks. In one embodiment, the inrush current is limited to 6 Aor less during the first 100 ms of power up. The system cart of FIG. 23,and other embodiments of the invention, is further comprised of systemcabling 2328. System cabling 2328 includes a main AC line cord; ACcordage for line filter, circuit breaker, power supply unit; AC cordageinside the power supply unit 2312; a computer unit 2310 power supplycord; monitor power supply cord; DVD drive power supply cord, a fan tray2326 power supply cord and other power cordages as used in theembodiments according to the invention. System cabling 2328 furthercomprises instrument electronics cables, which include instrumentelectronics sub-rack power cable; PCI Express cable; transducerconnector cable; mouse information system (MIS) cable; 3D stage cable;standby switch cable; etc. System cabling 2328 further comprisescomputer cables, which may include video extension cable(s) (VGA, DVI,SVideo, etc.); keyboard/mouse extension cable(s); keyboard splitter;mouse splitter; remote mouse cable; remote keypad cable; remote videocable; USB extension cable(s); Ethernet extension cable; printerextension cable; speaker extension cable, etc.

Cooling

Filtered ambient air is provided through the use of fans 2326 to thesystem cart electronics which include, for example, the beamformerelectronics (i.e., the beamformer card cage 2316, power supply unit2312, and computer unit 2310. The cooling system supports, for example,in one embodiment an ambient operating temperature range of +10 to +35°C., and the exhaust air temperature is kept below 20° C. above theambient air temperature, though other ambient operating ranges arecontemplated within the scope of this invention.

Electro-magnetic Interference (EMI) Shielding

In one embodiment, the exemplary system is provided with a contiguousEMI shield in order to prevent external electromagnetic energy frominterfering with the system operation, and to prevent electromagneticenergy generated by the system from emanating from the system.

The system shielding extends to the transducer cable 2304 and the array2302, and the transducer connector 2322. The computer 2310 and powersupply units 2312 maybe housed in separate shielded enclosures withinthe system. All shields are maintained at approximately groundpotential, with very low impedance between them. There is asubstantially direct connection between the chassis ground of the systemand earth ground. Also, in one embodiment the AC supply may be isolatedfrom the system power supply by an isolation transformer as part of thepower supply unit 2312.

Electronics Overview

An overview of an embodiment of the electronics for an exemplary systemaccording to the invention is shown in FIG. 24. In this view, theexemplary system comprises of a power supply unit 2402, instrumentelectronics subrack, and computer unit. The power supply unit 2402distributes both AC and DC power throughout the cart. A DC voltage of,for example, 48V is supplied to the instrument electronics subrackthough other voltages are contemplated within the scope of thisinvention. The instrument electronics subrack houses a beamformercontrol board 2404, four identical channel boards 2406, and a backplane2408. The boards 2406 mate with the backplane 2408 via, for example,blind mate connectors. The instrument electronics communicate with thecomputer unit via, for example, a PCI express connection 2410.

Channel Board

Exemplary channel boards are shown, and have been previously described,in reference to FIGS. 18 a-18 d. The channel boards 2406 generate thetransmit signals with the proper timing for transmit beamforming, andacquiring, digitizing and beamforming the receive signals. In thisexemplary embodiment of FIG. 24, there are four channels boards 2406,each containing 16 transmit channels and 16 receive channels Eachchannel board 2406 also contains 64 front end circuits, includingtransmit output stages, power supply circuitry, an FPGA for the transmitbeamformer, an FPGA to provide the partial sum of the receivebeamformer, the beamformer bus and connections to the backplane.

As can be seen in FIG. 18 a, four front end circuits are multiplexed toeach transmit and receive channel. There is one front end circuit foreach element in the array, and each front end circuit comprises atransmit output stage, transmit and receive multiplexer switches, adiode limiter, and components for receive filtering, as previouslydescribed in reference to FIGS. 18 a-18 d.

The transmit channels and transmit output stages generate bipolar pulsesat a specified frequency ranging from about 15 to about 55 MHz, with aspecified cycle count and amplitude. The transmit waveforms generated byeach channel have a specific delay relative to the other channels with aresolution equal to approximately 1/16 of the period of the transmitfrequency. The delay profile across the active transmit aperture iscontrolled by the transmit beamformer controller. A low jitter masterclock is used to generate the transmit burst signals. The transmitoutput stage includes a means of adjusting the peak to peak voltage on aper channel basis, in order to create an apodized transmit aperture.

The receive channels provide variable gain adjustment, filtering anddigitization of the receive signals, and receive beamforming. The gainis implemented with a variable gain amplifier which also acts as thepreamplifier. Gain is varied throughout the acquisition of theultrasound line according to a predetermined gain profile known as theTGC curve. Anti-aliasing filters precede the ADC (analog-to-digitalconverter) to prevent aliasing and to limit the noise bandwidth.

As shown in FIG. 18 a, dual ADCs 1807, 1808 are used for each channel,since the signal is acquired as a quadrature signal. The ADC clocks arephased 90° relative to one another. The sampling frequency is setaccording to the center frequency of the array being used. The 10 bitoutput of the ADCs is sent to a dual port RAM. The receive beamformerreads the quadrature samples and carries out interpolation filteringaccording to the dynamic receive focusing scheme which is controlled bythe receive beamformer controller. After interpolation filtering, theoutputs from each receive channel are summed and then sent to the CPUvia the high speed data transfer bus.

The receive beamformer is setup via the RX Control Bus. The transmitbeamformer is setup via the TX Control Bus. The control parameters areupdated before the start of each ultrasound line. The control parametersare TX aperture, TX delay profile (coarse and fine delay), RX aperture,RX delay profile (initial, coarse and fine delay), RX phase, and RXapodization. When all the control parameters are set and the system isready—a start-of-line (SOL) signal is sent to begin a transmit/receivecycle.

Transmit Output Stage

Multiplexing of the transmit channels occurs prior to the transmitoutput stage. Since the transmit beamformer can work with arrays with upto 256 elements, there are 256 transmit output stages, one per element.As shown and described in reference to FIGS. 20 and 21, each outputstage consists of two MOSFETs driving a center tapped transformer, withthe supply voltage at the center tap controlling the pulse amplitude.The output waveform is approximately a square pulse with a variablenumber of cycles. One end of the secondary of the transformer leads tothe array element, the other to the receive protection circuit. Reactiveimpedance elements provide impedance matching and filtering. A FETswitch in series with the gate of each MOSFET provides the multiplexing.The transformer and inductors are implemented, for example, as traces onthe printed circuit board. There is a ferrite core for the transformerwhich is inserted into an opening in the board.

Transmit Channel

Each transmit channel is multiplexed to four output stages as can beseen in FIG. 18. There are two transmit signals per channel, one todrive each phase of the push-pull output stage. As can be seen in FIGS.20 and 21, the analog section of the transmit channels consist of apush-pull type driver circuit capable of driving the gate capacitance ofthe output stage MOSFETs with the appropriate rise and fall times. Theseare multiplexed to the output stages by analog switches.

Transmit Beamformer

As can be seen in FIG. 22, the transmit beamformer uses DDR memory toproduce transmit waveforms clocked at a maximum of approximately 800MHz. Each channel uses a separate DDR memory output. The output clockrate is about 16×the center frequency (fc), thereby providing capabilityfor the appropriate delay resolution. Jitter is reduced by re-clockingthe DDR output with PECL. As can be seen in reference to FIG. 22A, witha clock rate of about 16×fc, transmit waveshaping can be effected, byadjusting the width of the positive or negative half cycles. Thiscapability can introduce “dead time” between the positive and negativehalf cycles to improve the shape of the output pulse.

Front End Circuit

For a transducer array comprised of 256 elements, there are 256 frontend circuit sections, one dedicated to each array element. As can beseen in reference to FIG. 17, each front end circuit comprises a frontend transformer 1702, a transmit output stage 1703, transmit MUX 1708, areceive MUX 1704, a diode limiter, and components for receive filtering.

Receive Channel

Also as can be seen in reference to FIG. 17, each receive channelcomprises the circuit elements which are involved with the acquisitionof the receive signal. The receive multiplexer 1704 connects the 64receive channels to the elements within the active aperture, which is asubset of up to 64 contiguous elements within the 256 element array.

Receive Beamformer

The receive beamformer, such as the one shown in FIG. 17, is a modulewhich independently processes and sums the digital data acquired by eachchannel in the receive aperture. Its functions may include, for example:dynamic control of the receive aperture size, i.e., the number ofchannels used during the acquisition of each receive sample; dynamiccontrol of receive apodization, i.e., the window applied to the receiveaperture; dynamic receive focusing, i.e., up sampling of the receivesignal and the adjustment of the delay applied to each receive channelduring the acquisition of each, sample, through the use of interpolationfilters and variation of aperture position within the array.

Channel Board Configuration

As shown in the exemplary system of FIG. 24, there are four channelboards 2406, each containing 16 transmit and 16 receive channels, allplugging into a backplane. Each channel board is assigned an addressbased on its position in the backplane to allow independent control ofeach board.

Beamformer Control Board

The beamformer control board 2404 of the exemplary system of FIG. 24provides and uplink of data to the host CPU (back end) and centralizedtiming and control for the hardware electronics. The link to host CPU isvia a PCI express bus 2410, which allows a data bit rate ofapproximately 250 MB/s in each direction per lane. An ×8 lane width PCIExpress link provides a peak full-duplex bandwidth of approximately 4GB/s.

The TX/RX controller 2412 provides master timing using start of frameand start of line synchronization signals to the transmit beamformer andreceive beamformer. It sets up the beamformer parameters in memory via acustom local bus. All the low-jitter clock frequencies for beamformingare generated on the beamformer control board 2404.

The RF partial sum data from each channel board 2406 is summed 2414together with synthetic aperture data 2416. Then the ray line data goesinto a first-in-first-out (FIFO) memory 2418 where it sits temporarilybefore being copied to the RF Cine buffer 2420. The RF Cine buffer 2420stores full frames of RF data and is randomly accessible. Data is readfrom the RF Cine buffer 2020 and copied to the host CPU via the PCIExpress link 2410. Alternatively, the data can be processed by thesignal processor module 2422 before being sent to the main computerunit. The data is then buffered, processed further and displayed by theapplication software and application user interface that runs on themain computer unit.

The data traffic control and reading/writing of control parameters isfacilitated by the embedded CPU 2424. The embedded CPU 2424 itself isaccessible by the host CPU via the PCI Express link 2410. Otherfunctions provided by the beamformer control board 2404 are thephysiological acquisition system and power supply monitoring. FIG. 19,previously referenced herein, is a block diagram of an embodiment of abeamformer control board 1900.

TX/RX Controller

Transmit beamformer control:

The transmit (TX) beamformer control updates the transmit beamformerparameters each transmit line. The parameters include number of coarsedelay cycles at the transmit center frequency (fc), number of fine delaycycles (at 16×fc), transmit waveshape (at 16×fc), number of transmitcycles, transmit select, and transmit voltage. The transmit beamformercontrol also schedules the updating of parameters for duplex mode,triplex mode, or multiple focal zones.

Receive beamformer control:

The receive beamformer control controls the receive delay profile,aperture size and apodization for each channel. The delay controlconsists of coarse and fine delays, which are controlled by the dualport RAM read pointer and the interpolation filter coefficient selectorbit, respectively.

The aperture control signal controls the aperture size dynamically byspecifying when the output of each channel becomes active. This is doneby controlling the clear signal of the final output register of theinterpolation filters. Dynamic receive apodization is controlled by fivebits of apodization data with which the signal in each channel ismultiplied. The receive control signals are read out from a control RAMat the input sample clock rate as shown in FIG. 26.

Transmit/Receive Synchronization:

A block diagram of transmit/receive synchronization is shown in FIG. 27.For B-Mode and M-Mode imaging different transmit and receive frequenciescan be used. However, line-to-line timing differences Oitter) betweenthe transmit cycle and receive cycle may be introduced because theclocks are asynchronous. A method to synchronize the transmit andreceive clocks is to use a programmable divider (TX_Divider) 2714 togenerate the receive clock (RXCLK_B) from the transmit clock (TXCLK×16)as shown in the embodiment of FIG. 27. The receive frequency is a fixedratio of the transmit frequency. The ratio is transmit clock frequencytimes 16 divided by N, where N is an integer. For example, in order togenerate a transmit clock frequency of 30 MHz and a receive clock(RXCLK_B) frequency of 26.7 MHz, the TX_Divider 2714 is set to divide by18. Due to the nature of the divider, RXCLK_B is in good phase alignmentwith TXCLK×16, and the two clocks always have a minimum phasedifference. RXCLK_B is used to synchronize the start of line trigger(SOL) 2702. The synchronized start of line trigger (SOL_S) 2704generates TX_TRG. TX_TRG is synchronized to TXCLK×8 by TX_TRG SYNC 2716.A delay between SOL_S and TX_TRG can be added if necessary. TX_TRGsignals the transmit beamformer to begin a transmit cycle. RXGATE issynchronized to RXCLK_B and signals the receive beamformer to begin dataacquisition. A multiplier (RX PLL) 2718 provides the RXCLK×4 clockfrequency that is needed by the I/Q Clock Generator 2720 to generate theI and Q clocks.

FIG. 27A illustrates an alternative method of maintaining consistentsynchronization between the transmit cycle and receive cycle by delayingthe start of line trigger (SOL) 2702 to a point when the phasedifference between the transmit clock and the receive clock is at aknown state. The SOL trigger 2702 is synchronized by the TX_RX_SYNCpulse. The TX_RX_SYNC pulse is generated by the TX_Sync Timer 2722. Thesynchronized start of line trigger (SOL_S) 2704 can now start thecontrol timing signals for the transmit beamformer 2706 and receivebeamformer data acquisition. TX_TRG is a delayed version of SOL_S thatsignals the transmit beamformer to begin a transmit cycle. TX_TRG issynchronized to TXCLK. The transmit beamformer 2706 generates the TXGATEmultiplexer control signals and TXA/TXB transmit pulses to the front endmodule. RXGATE signals the receive beamformer to start data acquisition.RXGATE is synchronized to RXCLK 2710.

The phase difference between transmit 2708 and receive clocks 2710 isfixed as long as the TX_Sync_Period 2712 is calculated correctly. TheTX_Sync_Period 2712 is the minimum number of transmit clock cyclesrequired to achieve synchronization. For example, if the transmit clockfrequency is 30 MHz and the receive clock frequency is 25 MHz,TX_Sync_Period 2712 will be 6 cycles of the transmit clock.

Clock Generator

The clock generator 2428 provides the appropriate clock frequencies fortransmit and receive beamforming. It comprises a low-jitter masterclock, a programmable divider, clock buffers and re-synchronizationcircuits. The frequencies are: transmit frequency (fc)—25 to 50 MHz;receive frequency—20 to 50 MHz in-phase and quadrature; digitalclocks—fc ×2, ×4, ×8, ×16. The fastest clock used in this exemplaryembodiment can be 800 MHz (50 MHz×16).

PCI Express Bridge

The PCI Express bridge 2426 connects the host CPU and the embedded CPU2424 via a PCI bus 2410. This allows DMA transfers from the RF cinebuffer 2420 to the host processor memory and vice versa. PCI Expressbuilds on the communication models of PCI and PCI-X buses. PCI Expressuses the same memory mapped address space as PCI and PCI-X with singleor burst read/write commands. However, PCI Express is a point-to-pointserial interconnect using a switch to connect different devices, whereasPCI and PCI-X are parallel multi-drop buses. PCI Express can be used asa chip-to-chip or board-to-board communication link via card edgeconnectors or over a cable.

The bandwidth of the PCI Express link may be, for example: Uplink—210MB/s burst and 140 MB/s sustained rate for RF Data, MIS Data, anddiagnostics; Downlink—20 MB/s burst and <1 MB/s sustained rate forwriting control parameters.

Synthetic Aperture FPGA

The partially summed beamformer RF data from the channel boards 2416 isfirst processed in the synthetic aperture FPGA. The processing comprisesbeamformer final summation, synthetic aperture and write to FIFO.

RF Cine Buffer

Functionally, the RF cine buffer 2420 is, for example, a 1 GByte dualport RAM. The RF cine buffer 2420 is a random access memory block thatstores RF data organized in lines and frames. The data can be input andoutput at different rates to support asynchronous signal processing. Thedata stream is made up of interleaved I and Q beamformed data. The FIFObuffer provides storage of the beamformer data while the memory is beingread by the CPU for the next display period.

In one embodiment, buffer specifications may include, for example:Storage—300 Full Size Frames (512 ray lines×1024 samples/line×32 bitsI&Q data); Buffer Size—>629 M bytes; Input rate—140 Mbytes/sec; Outputrate—140 Mbytes/sec (RF Data Rate) 32 Mbytes/sec (Video Rate).

Asynchronous Signal Processing

According to an embodiment of the described exemplary ultrasound system,it is capable of very high acquisition frame rates in some modes ofoperation, in the range of several hundred frames per second. Thedisplay rates do not have to be equivalent to the acquisition rates. Thehuman eye has a limited response time, and acts as a low pass filter forrapid changes in motion. It has been demonstrated that frame rates above30 fps have little benefit in adding to perceived motion information.For this reason, displayed ultrasound image information can be processedat a rate of 30 fps or lower, even when the acquisition rates are muchhigher. To uncouple acquisition from signal processing, a large RFbuffer memory is used to store beamformer output data. An exemplarystructure for buffering the beamformer output date is shown in FIG. 28.As shown in the FIG. 28, the memory buffer 2800 can hold many frames ofRF data. For a depth of 512 wavelengths, the storage of a full line of16 bit quadrature sampled RF uses 4 K bytes (1024 I,Q samples*32bits/pair). With 512 raylines per frame, a 1 G byte memory buffer canthen hold 512 2D frames. To keep track of frames written to the buffer,the write controller maintains “first Frame” and “last Frame” pointers,which can be read by the signal processing task, and point respectivelyto the first frame in the buffer available for reading, and the lastframe available for reading

During active acquisition, the beamformer summation output is written bythe Write Controller 2802 to the next available frame storage area,which is typically the storage area immediately following that pointedto by the “last frame” pointer. As the data in each new frame isacquired, the “first frame” and “last frame” pointers are updated sothat the data is written to the correct address in the buffer. Whenacquisition is stopped (freeze), the buffer then contains the last Nframes, with the “first frame” pointer indicating the oldest frame inthe buffer.

The signal processing module 2422 has access to the RF memory buffer2420. It accesses one acquisition frame at a time, at the display framerate to produce the displayed estimate data. While the system isscanning, a timer signals the signal processing module that a displayframe is required. At that time, the signal processing module 2422 willcheck to see if a new acquisition RF frame is available, and if so, willread the data and begin processing it. If the acquisition rate is fasterthan the display rate, the acquisition frames will be decimated prior toprocessing and display. After the system has been put in freeze, the RFframes stored in the memory buffer can be processed at any desired rate,up to the original acquisition rate.

Signal Processing Module

The beamformer control board 2404 comprises a signal processor 2422 inthe data path to reduce the data load and/or computation load on thehost CPU. The processor 2422 may be, for example, a FPGA with asufficient number of multipliers and memory, or a CPU such as, forexample, a 970 PPC or a general purpose DSP. The signal processingfunctions performed are divided between the signal processing module2422 on the beamformer control board 2404, and the main computer unit(i.e., host computer). They include post-beamforming gain control,B-Mode amplitude detection and log compression, PW Doppler spectralestimation, color flow clutter filter and frequency/power estimation,asynchronous signal processing or frame averaging. Factors that may beconsidered in deciding where the processing takes place include theprocessing speed required, the complexity of the process, and the datatransfer rates required.

B-Mode Signal Processing

For B-Mode imaging, the signal processing module 2422 performs processeswhich may include line interpolation, detection and compression.

Color Flow Imaging (CFI) Signal Processing

In one embodiment according to the present invention, Doppler color flowimaging is combined with B-Mode imaging such that the common blocks ofthe B-Mode signal path and the Doppler color flow signal path are timemultiplexed to provide both types of processing. Typically, the B-Modelines are acquired in between the CFI ensembles at rate of 1 or 2 linesfor each ensemble, depending on the relative ray line densities ofB-Mode and CFI (typical CFI images use half the ray line density ofB-Mode), as is known to one of ordinary skill in the art.

For CFI, the Signal Processing Module 2422 performs processes that mayinclude: ensemble buffering; clutter filter; velocity estimatecalculation; power estimate calculation and variance estimatecalculation.

After the I and Q waveforms from the receive beamformer summed outputhave passed through the clutter filter, the various parameters of theDoppler signal are estimated by a Doppler frequency and power estimatorin either the host computer or the CPU 2424 on the beamformer controlboard. The parameters estimated for each sample depth in the ensemblemay include Doppler frequency, Doppler power, and the variance of thefrequency estimates. These parameters may be used in a decision matrixto determine the probability that the frequency estimate is a trueestimate of the Doppler spectrum, rather than a noise or clutter signalestimate. Color flow velocity estimates are derived from the Dopplerfrequency estimates. All of the estimates are derived using a 2-Dautocorrelation method as is known to one of ordinary skill in the art.

PW Doppler Signal Processing

Pulsed Doppler acquisition may be either by itself, in duplex mode, orin triplex mode. In duplex mode, the PW Doppler transmit pulses areinterleaved with the B-mode transmit pulses so that the B-mode image isupdated in real time while the PW Doppler signal is acquired. The methodof interleaving depends on the Doppler PRF selected. The componentsshared between B-Mode imaging and Pulsed Doppler processing are timemultiplexed to accomplish both types of processing.

In triplex mode, Pulse Doppler is combined with B-Mode and color flowimaging. The simplest implementation of triplex mode is a timeinterleaving of either a B-Mode line or a CFI line, in a fixed sequencethat eventually results in a full frame of B-Mode and CFI image lines.In this implementation, the PRFs for both Pulsed Doppler and CFI arereduced by half, compared with their normal single modes of operation.

The I and Q samples for each ray line are range gated (a selected rangeof I or Q signals are separated out from the full range available andaveraged to produce a single I,Q pair), to select the region of interestfor the Doppler sample volume. The length of the range gate can bevaried, if desired, by the user to cover a range of depth. The resultingaveraged I,Q pairs are sent to a spectral processor, as well as an audioprocessor, which converts the I, Q Doppler frequency data to two audiooutput streams, one for flow towards the transducer (forward) and theother for flow away from the transducer (reverse).

For PW Doppler imaging, the signal processing module 2422 performsprocesses including range gating (digital integration).

M-Mode Signal Processing

For M-Mode imaging, the signal processing module 2422 performs processesincluding detection and compression.

EKV Signal Processing

EKV is an acquisition method in which extremely high frame rate imagesare generated (1000 frames per second and higher) as a post processingoperation using ECG (electro-cardio-graph) signals used as timingevents. EKV imaging may be implemented with either a single elementmechanically scanned transducer, or with a transducer array. EKV imaginginvolves the acquisition of ultrasound lines at a PRF of 1000 Hz orhigher at each line position in the 2-D image over a time period. Thetime period over which ultrasound lines are acquired at each lineposition, referred to as the EKV Time Period, can be for example, 1second, which is long enough to capture several cardiac cycles in amouse or other small animal. The acquisition of each ultrasound lineinvolves the firing of a single transmit pulse followed by acquisitionof the returning ultrasound data. For example, if there are 250 lines inthe 2-D image, a total of 250,000 ultrasound lines will be acquired inthe EKV data set. Each frame of the EKV image is reconstructed byassembling the ultrasound lines which were acquired at the same timeduring the cardiac cycle.

In one embodiment, the sequence of acquisition of the EKV data set maybe such that the ultrasound line position remains static while theultrasound lines are acquired over the time period. For example, if thetime period is 1 second, and the PRF is 1 kHz, 1000 ultrasound lineswill be acquired at the first ultrasound line position. The lineposition can then be incremented, and the process repeated. In this wayall EKV data for all 250 lines in the 2-D image will be acquired. Thedisadvantage of this method of sequencing is that length of timerequired to complete the full EKV data set can be relatively long. Inthis example the time would be 250×1 second=250 seconds.

In a preferred embodiment which makes use of an array, the method ofinterleaving allows for a reduction in the length oftime required tocomplete the EKV data set. For example if the PRF is 1 kHz there is a 1ms time period between pulses during which other lines can be acquired.The number of ultrasound lines which can be acquired is determined bythe two-way transit time of ultrasound to the maximum depth in tissuefrom which signals are detected. For example, if the two-way transittime is 20 μsec, 50 ultrasound lines at different line positions may beinterleaved during the PRF interval. If we label the line positions L1,L2 . . . L50, one exemplary interleaving method can be implemented asfollows: Position of acquired Time ultrasound line 0 μsec L1 20 μsec L240 μsec L3 . . . . . . 980 μsec L50 1000 μsec L1 1020 μsec L2 1040 μsecL3 . . . . . . 1980 μsec L50 2000 μsec L1 . . . . . .

The sequence in the above table is repeated until the EKV Time Periodhas elapsed, at which time there will be a block of data consisting of1000 ultrasound lines acquired at 50 different line positions, from line1 to line 50. The acquisition of the block of data is then repeated inthis manner for the next 50 lines in the 2-D image, line 51 to line 100,followed by acquisition over lines 101 to 150, etc., until the full 250line data set is complete.

The total time required for the complete data set over 250 lines isreduced by a factor equal to the number of lines interleaved, which inthis example is 50. Therefore the total length of time required would be5 seconds.

Embedded CPU

The embedded CPU 2422 on the beamformer control board 2404 is, in oneembodiment, a 32-bit embedded microprocessor with a PCI interface 2426and a DDR memory interface. The main function of the embedded CPU 2424is data traffic control. It controls data flow from the receivebeamformer FIFO 2418 to the RF cine buffer 2420, from the RF cine buffer2420 to the signal processing module 2422, and from the signalprocessing module 2422 to the host PC.

The beamformer control and diagnostics information is memory mapped onthe target PCI device as registers. The embedded CPU 2424 decodes thelocation of the registers and relays the information over theappropriate local bus. The local bus can be, for example, PCI, customparallel (using GPIO), I2C serial, or UART serial, as each are known inthe art.

Physiological Acquisition System

The physiological acquisition system 2430 (or “mouse acquisitionsystem”) filters and converts analog signals from the mouse informationsystem inputs 2438. These signals may include subject ECG, temperature,respiration, and blood pressure. After data conversion, the data istransferred to the embedded CPU 2424 memory via local bus, and then onto the host CPU for display via the PCI Express link 2410.

Power Suipply Monitoring

The beamformer control board 2404 monitors the rack power supply 2432and lower voltages generated on each board. For example, the rack powersupply 2432 may provide +48 VDC to the backplane 2408. In oneembodiment, two high voltage post regulators 2436 on each channel board2406 supply the transmit portion of the front end circuit. Thebeamformer control board 2404 monitors these regulators for over-currentor over-voltage situations

Backplane

The backplane 2408 mounts to the instrument electronics card cage. Inone embodiment it has blind mate edge connectors to allow each of theboards to plug in, though other connection schemes are contemplatedwithin the scope of this invention. It provides interconnection betweenboards, and input/output connectors for signals outside the card cage.In one embodiment, the size of the backplane is 8 U high by 84 HP wideso that it may fit in a 8U×19″ rackmount VME-style card cage. The cardcage depth may be 280 mm in one embodiment.

System Software

An overview of an embodiment of system software 2330 is shown in FIG.29. Generally, the system software 2330 operates on a processor platformsuch as, for example, an Intel processor platform running Windows XPoperating system. The processor platform of one embodiment of the systemis provided by the computer unit 2310, previously described herein.Alternatively, the system software 2330 maybe loaded on a standaloneworkstation for reviewing studies. The workstation does not containbeamformer hardware nor does it have a transducer for acquisition of newdata. It can review previously acquired study data and perform a limitedset of processing functions. For example, the user may add measurements,playback at different frame rates, or change the color map.

FIG. 30 is an embodiment of a main software application that maybe usedto practice one or more aspects of the present invention. The systemsoftware 3000, as shown in FIG. 30, may be loaded when the systempowers-up and can provide an interface for an operator of the system.

The framework 3018 which determines the overall structure of thecomponents can be used to produce an application executable by theoperating system of the processing platform of the computer unit 2310and to interface with the operating system. For example, the framework3018 may produce a Windows application and interface with the Windowsoperating system.

The application controller 3020 software component can be the statemachine for the system software 3000. It may control the interactionbetween the operator, the system software 3000 and the front end 2308.

The application view 3022 software component can provide a foundation tosupport the presentation of the system software 3000 based on the statemachine in the application controller 3020 software component aspreviously described herein.

The studies component 3002 may allow the operator to perform studies,review study data, edit content, and import or export study data. Aspreviously described herein, there can be various operating modessupported by the system for acquiring data and can be managed by a modes3004 software component of the system software 3000. The supported modesmay include, for example, B-Mode, 3D Mode, M-Mode, PW-Doppler, ColorFlow Doppler, etc. Each mode has adjustable parameters, cine loopacquisition, and main image display area, which may be managed by themodes 3004 software component. Some modes may operate simultaneously,e.g., PW-Doppler and B-Mode.

The beamformer control 3024 software component can generate the imagingparameters for the front end based on the settings in the systemsoftware 3000.

The user data manager 3006 software component may maintain userpreferences regarding how the system is configured.

The measurements 3026 software component may allow the operator to makemeasurements and annotations on the mode data.

The calculations 3028 software component may allow the operator toperform calculation on measurements.

The utilities layer 3008 software component contains common utilitiesthat are used throughout the application as well as third partylibraries.

The hardware layer 3012 software component is used to communicate to thebeamformer hardware via the PCI Express bus, as previously describedherein.

The physiological 3030 software component can be used to control thephysiological data collection through the hardware layer 3012 aspreviously described herein.

The data layer 3010 may contain a database of all the different sets ofparameters required for operation. The parameters maybe set depending onthe current user configuration and mode of operation.

The message log 3014 and engineering configuration 3016 may be used fordiagnostic reporting and troubleshooting.

Transducer Select Board

Referring back to FIG. 24, it can be seen that in this embodimentaccording to the present invention that the system can have onetransducer connector 2438 on the front of the cart and the user canphysically unplug the first transducer and then plug in another whenswitching transducers. In one embodiment this may be a 360-pintransducer connector 2438. In another embodiment, a transducer selectboard with two transducer connectors at the front panel can also be usedand enables switching between transducers without physically handlingthe transducers.

Example 2

Another exemplary embodiment of the high frequency ultrasound imagingsystem comprises a modular, software-based architecture described belowand as shown in FIG. 31.

The embodiment of FIG. 31 comprises four modules, which are part of aprocessing unit, for the exemplary system; a beamformer module 3102; anRF buffer memory 3104; a signal processing module 3106; and a system CPU3108. The beamformer module 3102 comprises the circuitry fortransmitting and receiving pulses from the transducer, as well as thedelay processing used for beamforming. Its output can be summed RF dataor optionally down-converted I and Q data from quadrature samplingtechniques. The output of the beamformer module 3102 may be written to alarge RF buffer memory 3104, as described herein.

The CPU/signal processing module 3106 is responsible for processing theRF data from the beamformer 3102 for image formation, or Dopplersensing. The signal processing module 3106 can comprise a CPU modulewith the processing tasks implemented in software executing in a generalpurpose computing environment. Alternatively, the signal processingmodule 3106 can be implemented with some signal processing functions inhardware or in software executing on dedicated processors, in which casean additional signal processing module can be implemented as a plug-incard to the system CPU 3108.

If a dedicated hardware solution is chosen for the signal processingmodule 3106, it can be implemented with high performance CPUs.Optionally it can be implemented with digital signal processing chips(DSPs). One type of DSP which may be used is of the floating pointvariety, as are known in the art, and can be controlled by the host CPU,as well as being “data driven.”The system CPU 3108 can act as both auser interface/control system as well as a signal/image processingsub-system. System control information can be distributed using memorymapped I/O, wherein modules interface to the peripheral bus of the CPUmodule. Optionally, the system CPU 3108 can be physically separate fromthe beamformer module 3102 and can be connected via a PCI Express cable(or equivalent) 3110. An exemplary PCI Express cable 3110 is one thatsupports transfers up to 1GB/sec and lengths of three meters. Some orall of the memory that exists on various modules can be mapped into theCPU's 3108 memory space, allowing for access to parameters and data.

The system CPU 3108 in the exemplary architecture can perform a numberof real-time processing tasks, including signal processing, scanconversion, and display processing. These tasks can be managed in amanner that does not require a “hard” real-time operating system,allowing for expected system latencies in the scheduling of processingroutines. In addition, the system CPU 3108 can be responsible formanaging the user interface to the system, and providing setup andcontrol functions to the other modules in response to user actions. TheCPU motherboard and operating system can support multiple CPU's, withfast access to a high speed system bus, and near real-time taskmanagement.

Transmit Beamformer

The beamformer module 3102 of this exemplary system comprises a transmitbeamformer. The transmit beamformer can provide functions which mayinclude, for example, aperture control through selection of a subset ofarray elements, delay timing to start of transmit pulse, transmitwaveform generation, and transmit apodization control. For thisexemplary embodiment, a transducer array 3112 is utilized. In oneembodiment, this transducer array 3112 contains up to 256 elements. Toeliminate the need for high voltage switching of transmitter pulsedrivers to transducer elements, the transmit beamformer component of thebeamformer module 3102 may be comprised of a number of transmittersequivalent to the number of transducer array elements. For instance, inan exemplary array transducer having 256 elements the transmitbeamformer comprises 256 transmitters. Optionally, the transmitbeamformer can comprise less than 256 transmitters and a high voltageswitching method to connect an individual transmitter to a specificelement. High voltage multiplexers are used to select a linear subset ofelements from a 256 element array.

Optionally, the transmit beamformer component of the beamformer module3102 may comprise high voltage pulser drivers for all 256 elements ofthe exemplary array, and a switching mechanism which connects a subsetof transmit waveform generators to the appropriate drivers/arrayelements. This optional embodiment uses 256 TX/RX switches forprotection of the receiver inputs with low level multiplexing to selectthe subset of array elements for the receive aperture. The low levelmultiplexing can optionally be combined with the TX/RX switches and insome cases has less attenuation of the receive signals and fasterswitching, when compared with a high voltage MUX scheme.

Transmit delays of 1/16 wavelength can be used and provide appropriatefocusing and side lobe reduction in the transmit beam. For desiredsteering and focus control, the maximum delay times, when measured inwavelengths, can be at least 0.7 times the largest transmit aperture.For example, with 128 transmitters and an array spacing of1.5wavelengths, the largest transmit aperture is 192 wavelengths. At 20MHz center frequency, the maximum transmit delay times can be at least6.72 microseconds.

For 1/16 wavelength accuracy, the highest center frequency of interestspecifies the delay resolution. At 50 MHz, this gives a delay accuracyof 1.25 nsec, which uses the equivalent of an 800 MHz clock and a 13 bitcounter to achieve the maximum delay time of 6.72 usec. Optionally,instead of a high frequency clock a four phase clock at 200 MHz can beused. This would allow selecting a specific transmit delay by selectingone of the four phases of the 200 MHz clock as input to an 11 bitcounter, which is preloaded with the number of 200 MHz clocks in thedelay time.

The transmit beamformer component of the beamformer module 3102 furthercomprises a bi-polar transmit pulser. This type of pulser drive istypically specified with three parameters: T1, which is a transmitfrequency (duration of half cycle); T2, which is a half cycle on time(duration of either positive or negative half cycle pulse); and T3,which is a pulse duration (number of half cycle pulses in totaltransmit). These durations are shown in FIG. 32.

The control of the half cycle pulse duration, T2, allows for closerapproximation to a sine wave drive, with improved transducer output. Itcan also be used to obtain a somewhat crude apodization of the transmitpulse power, provided that sufficiently fine control of the duration isprovided.

Transmit apodization can be used to reduce spurious lobes in thetransmit beam, which can be either side lobes or grating lobes.Apodization of the transmit aperture results in reduced power output andworse lateral resolution, so it is not always desirable. Often a smallamount of apodization capability, such as providing for only a fewlevels of power output, is sufficient to achieve a good compromisebetween spurious lobe reduction and lateral resolution. The pulse widthmodulation scheme mentioned above for transmit waveform generation isone possible means of providing limited transmit apodization. A secondmethod is to provide not one, but possibly four or more levels of highvoltage for the pulser drivers, with a means to select one of theselevels on each pulser.

Receive Beamformer

The beamformer module 3102 also comprises a receive beamformercomponent. There are several different receive beamformingimplementations which can be used in the exemplary system. The digitalmethods discussed below have least one A/D converter for each element inthe receive aperture. In this exemplary embodiment, the A/D converterbit depth is 10 bits, which gives the desired beamforming accuracy at−50 dB signal levels. The A/D dynamic range is chosen to reduce spuriouslobes and thus provide contrast resolution as desired. Eight bit A/Dconverters can be used if appropriate. Embodiments of the exemplarysystem use 64 receive channels, combined using synthetic aperture toimplement a 128 channel receive aperture for applications where maximumframe rate is not needed. One optional method for digital receivebeamforming implementation samples the ultrasound signals from theindividual elements at a rate which is at least twice as high as thehighest frequency in the signal (often called the Nyquist rate.) Forexample, a 50 MHz, 100% bandwidth transducer the Nyquist sampling rateis 150 MHz or higher.

Bandwidth Sampling

Another optional sampling method for the receive beamformer component ofthe beamformer module 3102 is bandwidth sampling. Sampling theory, asknown to one skilled in the art, provides that if a continuous functiononly contains frequencies within a bandwidth, B Hertz, it is completelydetermined by its value at a series of points spaced less than 1/(2*B)seconds apart. Sampling a band-limited signal results in multiple copiesof the signal spectrum appearing at a fixed relationship to the samplingspectrum. Provided these replicated spectra don't overlap, it ispossible to reconstruct the original signal from the under-sampled data.For example, consider a signal with a maximum bandwidth of 20 MHzcentered at 30 MHz, and sampled at a rate of 40 MHz. In this situation,the spectrum is replicated as shown in FIG. 32. The original spectrum isreplicated in the 0-20 MHz portion of the frequency spectrum (it is alsoreflected about the fs/2 frequency, but this can be accounted for insubsequent signal processing), where the 40 MHz sample rate is adequateto preserve all the information in the signal.

FIG. 33 illustrates bandwidth sampling of 30 MHz signal spectrum, whichmay be utilized in an embodiment of the receive beamformer component ofthe beamformer module 3102. Sampling the signal spectrum in FIG. 33using normal Nyquist sampling requires a sample rate of 80 MHz orhigher. Using bandwidth sampling at ¾ of the wavelength, as describedabove, transducer center frequencies up to 60 MHz can be managed with 80mega samples per second (MSPS) 10 bit A/D converters, which are known inthe art and are available from several vendors. In the example givenabove, the signal spectrum had no frequency components outside of the 20MHz bandwidth region (66.7% of the center frequency). In practice, atransducer spectrum often has skirts that can extend beyond the 66.7%bandwidth region, creating overlapping spectra and inaccurate signalreconstruction. These skirts can be dealt with by using a bandpassanti-aliasing filter prior to the A/D converter that keeps the power inthe spectral skirts extending beyond the bandwidth limits to a desiredlevel, such as 5-10%.

Quadrature Sampling

Another form of bandwidth sampling, known as quadrature sampling, canoptionally be used in an embodiment of the receive beamformer componentof the beamformer module 3102. In this sampling method, two samples aretaken at 90° phase with respect to the center frequency. These samplescan be repeated at an interval which is consistent with the bandwidth ofthe signal. For example, if the quadrature samples are taken at everyperiod of the center frequency, the sample rate supports a 100%bandwidth signal. The sample pair resulting from quadrature sampling isnot a true complimentary pair, since the samples are taken at differenttimes, however they are true samples of the analytic waveforms, andconcurrent quadrature samples can be found by interpolating the samplesof the two I and Q sampled waveforms to the same point in time.Quadrature sampling may be implemented with one high sample rateconverter sampling at four times the center frequency or with two lowerfrequency converters each operating at the center frequency but withclocks differing in phase by 90° with respect to the center frequency

Nyguist Sampling

Optionally, yet another form of sampling can be used in the receivebeamformer. This form of sampling is Nyquist sampling combined withbandwidth sampling. Normal Nyquist sampling is used for the lowertransducer center frequencies and bandwidth sampling for the higherfrequencies. Commercially available 10 bit A/Ds with maximum samplerates of 105 MSPS are available. With this sample rate capability, a 30MHz center frequency transducer with 100% bandwidth can be sampledadequately at Nyquist rates. At 40 MHz, Nyquist sampling can be used fortransducers with bandwidths up to approximately 60%, so for this centerfrequency or higher, bandwidth sampling can be used. If these highersample rates are used, the beamformer processing circuitry alsoaccommodates the higher clock rates and increased storage requirements.

A variation of quadrature sampling can be used to provide a higherbandwidth beamforming capability for those applications that can benefitfrom it (for example, harmonic imaging) In this method, two quadraturesample pairs may be acquired for every cycle of the center frequency.For example, consider the sampling of a signal which has a centerfrequency of 30 MHz and significant spectral content beyond 100%bandwidth, such that the spectrum extends to frequencies less than 15MHz and/or greater than 45 MHz. Two A/D converters per channel may beused to acquire the RF signal at that channel, each samplingperiodically at twice the center frequency, 60 MHz. The sample clock ofthe second A/D converter is delayed by ¼ the period of the 30 MHz centerfrequency relative to the sampling clock of the first A/D converter.Every second sample acquired by the A/D converters will be multiplied by−1. The sample stream originating from the first A/D converter will thenbe the down-converted quadrature (Q) sample stream, and that originatingfrom the second A/D converter becomes the down-converted in-phase (D)sample stream. The fine delay required for receive beamforming may beimplemented by interpolation of the quadrature samples. This methodallows for accurate sampling of the RF signal over 200% bandwidth of thecenter frequency.

In an alternative method of providing higher bandwidth beamformingcapability which requires one A/D converter per receive channel, the RFoutput of the beamformer can be formed using two acquisition pulses,similar to a synthetic aperture approach. For example, consider a 30 MHzsignal spectrum with 100% bandwidth, so that the −6 dB spectrum extendsfrom 15 to 45 MHz. In this case, the signal can be sampled at a 60 MHzsample rate, and the sign of every other sample flipped, to provide adown-converted sample stream that can be taken as the Q channel of aquadrature down-conversion scheme. On the next acquisition, the samplingclock is delayed by ¼ of the period of 30 MHz, providing (after flippingthe sign of alternate samples) the I quadrature waveform. These twoquadrature waveforms are then time shifted and combined afterbeamforming to reconstruct an RF signal that is accurate for 200%bandwidth of the 30 MHz center frequency. This is adequate to captureall the information from an ultrasound transducer with 100% bandwidth.The frame rate is reduced by half compared with single pulse ray lineacquisition. Higher frame rates can be achieved over a region ofinterest by reducing the number of image lines.

In the exemplary embodiment of FIG. 31, receive beamformer delayimplementation is performed using the interpolation method. In thisapproach to beamforming, the A/D converters all sample concurrently, ata constant sample rate (using bandwidth or quadrature sampling). Thedelays for steering and dynamic focusing are implemented in twosteps: 1) a coarse delay stage that implements a delay which is anintegral number of sample clocks cycles, and 2) an interpolation filterthat interpolates to 1/16 of a wavelength time positions in between thecoarse samples. The coarse delay stage performs the function of aprogrammable shift register, whose maximum length is equivalent to themaximum delay time desired in sample periods. The order of these twostages can be reversed if desired, depending on implementationconsiderations.

Bandwidth sampling interpolation may be described using the followingexample. For an exemplary 30 MHz array using bandwidth sampling, thesample rate on all A/D converters canbe set to 40 MHz, providing a 66.7%bandwidth. With 128 receive channels, about 10 micro-seconds is desiredfor maximum delay, thus implementation uses a programmable shiftregister of about 400 stages. At 40 MHz, the programmable interpolatorsneed only calculate one of eleven intermediate sample values (for 1/16wavelength accuracy), equally spaced between adjacent 40 MHz samples.The interpolators can be specifically designed for bandwidth sampling toprovide for accurate signal reconstruction. Samples can be taken fromthe output of all channels' interpolators, and summed to produce thesampled RF waveform for the desired beamforming direction.

The signal reconstruction process for interpolating between bandwidthsampled data points is simplified for the example 30 MHz array givenabove. In this case, every odd sample can be taken as samples of the Qcomponent of the quadrature baseband representation of the signal (withalternate sign), while even samples can be considered to be samples ofthe I component. A simple bandlimited interpolator can be used to findthe I and Q signal values at the appropriate intermediate time point,which can then be combined to reconstruct the RF value. If desired, allof the bandwidth sampled data points can be down-converted by theinterpolation filters, resulting in a baseband quadrature sampledbeamformer output, which can simplify downstream signal processing.

Quadrature sampling interpolation maybe described using the followingexample. In this example, the input signals for each channel are assumedto be quadrature sampled, at one quadrature pair per cycle of thetransducer center frequency, providing an input bandwidth of 100% aroundthe center frequency. The two samples in the pair are taken at 90degrees phase difference with respect to the center frequency, whichprovides actual samples of the Q and I baseband signals, but thewaveforms are sampled at different points in time. Before the Q and Idata can be combined, this sampling offset is corrected usinginterpolation filters. The interpolation required for correcting thesample offsets can optionally be incorporated into the interpolationfilters used for beamforming.

Since the quadrature sampling method proposed generates baseband I and Qsignals, the interpolation filters are operating on these signals,rather than the RF waveforms. The samples for all channels are taken atthe same time, which leads to I and Q waveforms with the same phaserelative to an RF waveform common to all channels. This is equivalent tousing mixers on all channels to derive I or Q signals, where the carrierfrequency for the mixers all have the same phase. However, correctsummation of the I and Q samples from different channels can be providedby adjusting the carrier phase on each channel to match the phase of thetime delayed echo waveforms. This amounts to a phase rotation of theinterpolated I, Q samples according to the interpolation point relativeto 0 degrees phase of the RF center frequency period. This rotation canalso be incorporated into coefficients of a FIR interpolation filter, toproduce a corrected I and Q output from each channel that can be summedcoherently.

As way of explanation of the quadrature sampling interpolationbeamforming method, one can first consider a simpler conceptual model,rather than an actual implementation. In this model, interpolation willbe implemented to 16 separate points over the period of the centerfrequency, providing 1/16 wavelength accuracy for beamforming. Thislevel of accuracy has been shown to be sufficient to provide nosignificant degradation ofbeam profiles. Considering a quadraturesampled waveform as shown in FIG. 34, the signal is a sine wave whosefrequency is 0.9 times the frequency of sampling (which is, for example,1 Hz in this instance). The Q samples are shown as ‘o’s 3402, while theI samples are shown as ‘x’s 3404. As can be seen from the figure, the Qand I samples are samples of much slower changing waveforms, whichrepresent the baseband Q and I waveforms. The interpolation filtersoperates on these waveforms, to compute 16 interpolation points perperiod of the sampling frequency.

Referring to FIG. 34, which shows a quadrature sampled sine wave at 0.9times the sample frequency. The interpolation points are chosen so thatthe actual sample values don't fall on an interpolation point. Thisprovides that the filter function inherent in the interpolation filteris applied to all points. The positions of the 16 interpolated pointswith respect to the Q and I sample points are shown in FIG. 34A.

Typically, a four point FIR filter is sufficient for accurateinterpolation. To interpolate the points 0-3, between Q and I samples, awindow of eight samples can be used, as shown in FIG. 34B.

To interpolate the points 4-15, the window is moved forward by onesample, as shown in FIG. 34C.

Using these windows, a set of eight coefficients for each interpolationposition can be computed, which when multiplied times the sample valuesin the window, yields the interpolated I and Q values. In the case ofthe first window, the interpolated I value would be the sum of the evennumbered products (0,2,4,6) while the Q values would be the sum of theodd numbered products (1,3,5,7). In the case of the second window, the Iand Q values would be reversed.

FIG. 35 is a plot of the interpolated values for the example sine wavegiven in FIG. 34 over the sine wave of FIG. 34. In the figure, theinterpolated points are shown as the dotted lines and start after thefourth sample point, which is the first position that a window can beapplied (in this case, window #2).

FIG. 36 is an illustration of a data set for the acquisition of a singleray line of echo information from a linear array, consisting of thequadrature sampled signals from each of the transducer elements over adepth range. This data set can be viewed as an array with depth 3602along one axis and channel number 3604 along the other. To reconstruct asingle range point along the ray line from the data set above, an eightsample window is positioned in each channel's data row at theappropriate sample number, which corresponds to depth, and one of the 16interpolation points is chosen which provides the exact delay required.As shown in FIG. 36, the various channel windows are positioned along aparabolic arc 3606, which corresponds to the curvature of focus neededto reconstruct the range point. The beamforming parameters for the rangepoint are then defmed by providing a starting sample number andinterpolation number for each channel included in the aperture.

After applying the appropriate interpolation filters to each of thechannel data shown above, and I and Q sample is obtained for eachchannel that corresponds to the appropriate delay for the range point.As previously described herein, these I and Q sample pairs can not besimply summed to derived a beamformed I,Q pair, since the phase of theI,Q sample from each channel is different. Before the I,Q pairs fromeach channel can be summed, each channel's I,Q pair is phase rotated tocorrespond the same phase with respect to the delay time implemented.For example, if two channels are receiving an echo return, where thepath length difference to the range point corresponds to exactly ½wavelength of the echo frequency, and these echo returns are sampled atthe same times by our quadrature sampling scheme, the samples will fallon different points on the RF signals, and the resulting I,Q waveformswill be 180 degrees out of phase. This situation is illustrated in FIGS.37A and 37B, in which the reconstruction points on the waveforms of thetwo channels are indicated by the vertical lines. When the I and Qvalues at the reconstruction point from the waveforms of the twochannels are summed in the beamformer they should add constructively,however, it is apparent that the values are quite different and will notadd constructively. To sum the two I and Q values a vector rotation mustbe performed first. The amount of rotation is calculated by determiningthe distance of the reconstruction point from the start of a sampleperiod, which is effectively the interpolation point number times 1/16wavelength (plus 1/32 of the period, to be precise). This distance canbe converted into an angle by taking the fraction of the total periodand multiplying by 2*pi. The rotation equations are then given below:Qr=I*sin (angle)+Q*cos (angle)  (1)Ir=I*cos (angle)−Q*sin (angle)  (2)

Using these rotation equations on the interpolated I and Q samplesallows the rotated I's and Q's to be summed coherently. The rotation ofthe I and Q samples can be incorporated into the 8 coefficients used forinterpolation. For example, when using the first interpolation window,where the even samples are I samples, the sin (angle) in equation (1),above, can be multiplied by each of the I coefficients, and the cos(angle) term multiplied by each of the Q coefficients. The resulting FIRfilter then provides the rotated Q value, when all product terms areadded together. Similarly, another set of coefficients can be used tocompute the rotated I value. In this scheme, the FIR filter operatestwice per sample period, using different coefficients, to produce anoutput stream of rotated Q and I values. This stream can be summed withthe stream of rotated Q and I values from other channels to produce thebeamformer output, which in this case is interleaved I,Q datarepresenting the down-converted summed RF. Alternatively, theinterpolation of the Q and I values may be implemented with separate FIRfilters, each with 4 coefficients. In this scheme, the phase rotation isimplemented in a stage following the interpolation.

The sampling scheme in which two quadrature pairs are acquired for eachperiod of the center frequency also requires a phase rotation afterinterpolation of the quadrature samples. In this scheme two A/Dconverters per channel may be used to acquire the RF signal at thatchannel, each sampling periodically at twice the center frequency. Thesample clock of the second A/D converter is delayed relative to thesampling clock of the first A/D converter by ¼ of the period of thecenter frequency. Every second sample acquired by the A/D converterswill be multiplied by −1. Interpolated values can be calculated for 16separate points over the period of the center frequency, or for 8 pointsover the period of the sample clock. The interpolation points calculatedover a span of two sample clock periods may be numbered from 0 to 15.The amount of phase rotation required is the interpolation point numbermultiplied by 2*pi/16. For example, when the interpolation point islocated at ⅛ of a sample clock period after the start of odd numberedsample clock cycles, the amount of phase rotation will be 2*pi/16. Whenthe interpolation point is located at ⅛ of a sample clock period afterthe start of even numbered sample clock cycles, the amount of phaserotation will be 2*pi*( 9/16). The interpolation points may be shiftedby 1/32 of the center frequency so that the actual sample values don'tfall on an interpolation point on order to ensure that the filterfunction inherent in the interpolation filter is applied to all points.After the phase rotation, the values can be summed to provide thebeamformer output. The amplitude of the envelope of the received signaloutput from a quadrature beamformer may be determined by calculating thesquare root of the sum of the squares of the I and Q samples. Acompression curve may then be applied to the envelope amplitude values.Doppler processing can use the summed I and Q sample stream directly toderive Doppler frequency estimates and/or compute FFT spectral data.

A possible implementation for interpolation filters operating onquadrature samples is described below. In one embodiment theinterpolation filters and control logic can be implemented with an FPGAdevice. As provided above in reference to FIG. 31, receive beamformerdelay implementation may be performed using the interpolation method. Ahigh level diagram of a delay implementation is shown in FIG. 25. Thisdiagram shows the fimctions after A-to-D conversion for a singlebeamformer channel. The outputs of the two A/D converters aremultiplexed into a single sample stream at a constant rate of two timesthe center frequency. For 10 bit A/D converters, we then have a seriesof 10 bit samples coming from the A/D converters, with the first sampledesignated as a Q sample, followed by the I sample of the quadraturepair. This stream is the input to the dual port ram 2502 shown in FIG.25.

At the start of an acquisition line, a write pointer 2504 and a readpointer 2506 in the dual port ram are reset to the top of the ram 2502.As each new sample comes in, the sample is written to the ram 2502 atthe address of the write pointer 2504, which is then advanced to thenext sequential location. When the write pointer 2504 reaches the end ofthe ram 2502, it wraps around to the beginning of the ram 2504 for thenext write operation. The dual port rams 2502 are large enough to storesamples for the maximum delay required by the steering and focusingneeded for the acquisition line.

The input side of the dual port ram 2502, with the writing of each newsample and subsequent incrementing of the write pointer 2504, needs nochannel unique control mechanism, since all channels can write theirinput data at exactly the same time and to the same addresses. Theoutput side of the dual port ram 2502 uses independent channel control.FIG. 26 illustrates one mechanism for implementing the control signalsrequired for a single channel. In the embodiment of FIG. 26, a controlram's 2602 address is incremented at the input sample clock rate (2×thecenter frequency, Fc). The ram 2602 then provides a registered output2604 where each bit provides an independent control signal.

Returning to FIG. 25, it is shown and described how the receive delaysare implemented in one embodiment according to the present invention.For echoes returning from a point located along the centerline of thereceive aperture, the echo first appears in the signals from the elementor elements closest to the center of the aperture, then later in theelements near the outer portion of the aperture. This means that toalign echoes in signals from the center and the outer edge of theaperture, the center signals can be delayed a period of time before theycan be summed with the signals from the outer edge. In the dual port ram2502 example, longer delays are achieved by letting the read point 2506lag further back behind the write point 2504. Therefore, the centerchannel in the aperture will have the greatest difference between readpoint 2506 and write point 2504, while the outer channels will have thesmallest difference.

For dynamic focusing, the focal point is moved outward along the receiveline at the half the speed of sound, so that focal point is always atthe location of the echo being received. For a constant aperture, as thefocal point moves out in range, the delay between the center and outerchannels of the aperture decreases. With dynamic aperture, or constant f(i.e., focal length divided by the aperture size) number operation, thedelay between inner and outer channels increases until the maximumaperture is reached, then the delay decreases.

Using dynamic aperture and dynamic focus with the dual port ram delayscheme, yields the following operation of the dual port ram pointers2504, 2506: The center channel is delayed by the maximum delay amount(the amount for the full aperture) by letting the write pointer 2504move ahead of the read pointer 2506 until the delay is achieved. At thatpoint, the read pointer 2506 is moved ahead at the same rate as thewrite pointer 2504. An outer channel's initial delay is set by lettingthe write pointer 2504 move ahead of the read pointer 2506 by theappropriate amount. This initial delay offset can be less than theoffset of the read 2506 and write pointers 2504 of the center channel.At this point, the read pointer 2506 is moved ahead at the same rate asthe write pointer 2504 until the channel is made active in the aperture.

After a channel is made active in the aperture, its delay graduallyincreases with time to approach that of the center channel. This isaccomplished by occasionally not moving the read pointer 2506 ahead whenthe write pointer 2504 is moved. This increases the offset between theread 2506 and write pointer 2504 gradually with time.

The above operation can be directed with only two binary state controlsignals as shown in FIG. 26A. The first signal is a read pointer advanceenable (RPE) 2600, which allows the read pointer 2506 to advanceconcurrently with the write pointer 2504. When this signal is true atthe time of the Fc*2 sample clock, the write pointer is advanced afterthe data is written to the dual port ram 2502, and the read pointer 2506is advanced at the same time. When the signal is false, the writepointer 2504 is advanced following a write operation, but the readpointer 2502 remains the same. The RPE control signal 2606, 2606 a isused not only to set the initial delay of a channel, but also toimplement the dynamic focus coarse delays. The second control signal(CE) 2608, 2608 a merely specifies when the channel's output becomesactive, so that it participates in the summation of all active channels.This can be accomplished by the CE signal 2608, 2608 a controlling the‘clear’ input of the fmal output register of the interpolators. Achannel is made active in the aperture according to when its elementsensitivity pattern allows it to receive the returning echoes with lessthan some threshold amount of attenuation. This time must be consistentwith the initial delay time implemented by the first control signal. Itshould be noted that the CE signal 2608 specifies the time a channelbecomes active in terms of the number of quadrature samples from thestart of the acquisition line. This is because when a channel firstparticipates in the sum of channels, it must contribute a quadraturepair. In the case of the Fc*2 sample clock, there are two clocks forevery quadrature sample pair.

FIG. 26 illustrates the control signals as they might appear for acenter element (2606 and 2608), and an element at the outer edge (2606 aand 2608 a) of the full aperture. However, with an even number ofchannels/elements, there is no actual center element, since the centerof the aperture falls between two elements.

For the center channel, RPE 2606 is held low for the maximum delay timeneeded. This allows the write point 2504 to move ahead while the readpoint 2506 stays put. After the delay time is reached, RPE 2606 is sethigh (true) to allow the read pointer 2506 to advance at the same rateas the write pointer 2504. Since there is no dynamic focus required forthe center channel, RPE 2606 remains high for the remainder of theacquisition line. The center channel CE signal 2608 brings the channelactive shortly after the delay time is reached. The offset is to allowthe shift register and register used for the interpolation filter tofill. The CE signal 2608 then removes the clear on the output registerso the channel's data can enter the summation bus.

For the outer channel, RPE 2606 a is held low for only a short time,since its initial delay is much shorter than the center channel. ThenRPE 2606 a is set high, allowing this delay to be maintained until thechannel is made active. At that time, the RPE signal 2606 a is set lowfor a single clock cycle occasionally to implement the dynamic focuspattern. The CE signal 2608 a removes the clear on the output registerwhen the channel can participate in the summation.

Referring back to FIG. 25, the interpolation filters provide the finedelay resolution for beamforming. There are 16 interpolation points perwavelength of the center frequency, providing 1/16 lambda delayresolution. For each interpolation point, two eight point FIR filtersare applied—one to generate the analytic signal I sample, and the otherto generate the Q sample.

This means that the interpolation filter operates twice per period ofthe center frequency, or at the Sample Clk (Fc*2) rate. The I and Qsamples are output in succession to the output register, which ifenabled, feeds the samples into the summation bus.

The input for the interpolation filters comes from the read address ofthe dual port ram 2502, which typically advances by one sample (I or Q)for each Sample Clk (Fc*2). When a read is performed of the dual portram 2502, the sample is input to an eight sample shift register 2508,which holds the last eight samples read. If the read operation of thedual port ram 2502 is not enabled (RPE low), then no data enters theshift register 2508, and the read pointer 2506 is not advanced. Theshift register 2508 still holds the last eight samples, and no samplesare lost when the read pointer 2506 does not advance; the read pointer2506 simply falls further behind the write pointer.

Every two sample clock cycles, the samples in the shift register 2508are transferred in parallel to the inputs of the interpolation filtermultipliers 2510. There they remain for the two multiply/accumulateoperations that generate the I and Q outputs. When no dynamic focusingis occurring, the samples moved to the multiplier inputs shift forwardin time by two samples for each center frequency period. The filter thenoutputs an I and Q sample for each period of the center frequency. Withdynamic focus, occasionally the read cycle of the dual port ram isdisabled, and the samples moved to the multiplier inputs shift forwardby only one sample. This allows the interpolation point to move forwardin time by less than a full period of the center frequency. With dynamicfocus on an outer channel, the interpolation point is gradually movingback in time, towards the same time as the center channel.

The coefficients used by the interpolation filters are stored in a smallram 2512, which can be loaded by the system CPU. The ram 2512 can hold32 sets of coefficients, 16 for the I interpolation point and 16 for theQ interpolation point. The coefficients are selected by five addresslines, four of which are control lines that come from the control ram2602. These four lines must provide a new address every other sampleclock (Fc*2). The other line selects the I or Q coefficient set for theinterpolation point chosen, and can be toggled with the operation of thefilter, producing an I and Q sample every period of the centerfrequency. Finally, the output register 2514 for the interpolationfilter holds the output samples before they enter the summation bus.This register's clear input is controlled by the CE control line. Thisallows a channel to be disabled from contributing to the sum bus untilthe interpolation output is valid.

Another way to implement the interpolation filters, phase rotation anddynamic apodization is shown in FIG. 25B. In this figure, all digitalcircuit elements in the upper box 2520 which require a clock are clockedat the receive frequency clock. All digital circuit elements in thelower box 2522 which require a clock are clocked at twice the receivefrequency clock. The input I/Q data from the analogue to digitalconverters (ADCs) 2524, 2526 are written to separate FIFOs 2528, 2530.The samples output from the ADCs 2524, 2526 may undergo an offsetcorrection in which a predetermined constant value is added. The samplesfrom the output of the ADC offset correction stage 2524, 2526 are storedsimultaneously into the FIFOs 2528, 2530, so the writing of the newsample into the FIFOs does not require separate timing logic. All thechannels share the same write enable signals. The read side of the FIFOof each I and Q channel 2528, 2530 uses independent read enable signals2532, 2534, controlled by receive delay signals generated by theBeamformer Controller.

The start of the read enable signals 2532, 2534 of each FIFO is delayedby a number of receive clock cycles equal to the initial coarse delayvalue 2536 required for each channel. If the read enable signal 2532,2534 is held low while data is written into the FIFO 2528, 2530, theread out of the FIFO will be suspended and the coarse delay 2536 willincrease. When the read enable signal 2532, 2534 goes high, the coarsedelay 2536 that is applied remains constant. To align echoes in thesignals from the center and the outer edge of the aperture, the centersignals will be delayed a period of time before they can be summed withthe signals from the outer edge. The delay value for sampled data at thecenter of the aperture is greater than that of the outer edges.

Dynamic receive focusing requires a control signal DF 2538 which goeshigh when the interpolation filter index 2540 needs to be changed. Theinterpolation filter index 2540 is a modulo 16 number ranging from 0 to15. The interpolation filter index 2540 will decrease when theinterpolation point has shifted by 1/16 wavelength. When theinterpolation filter index 2540 decreases from 0 to 15, the FIFO readenable signal 2532, 2534 will go low for one clock cycle, to increasethe coarse delay 2536 by one.

The fine delay is implemented by interpolation. In this example, theinterpolation filters are implemented as systolic FIR filters with 4taps 2542, 2544, 2546, 2548. There are 16 sets of coefficients for the16 interpolation points. Each interpolation point has 4 coefficients2550, 2552, 2554, 2556. By interleaving the I and Q samples andoperating the filter at twice the receive clock frequency, the sameinterpolation filter can be used for both the I and Q samples. Differentsets of coefficients are used for the I and Q interpolation, since the Iand Q samples acquired by the ADCs are sampled at different points intime but are interpolated to the same point in time. To correct thesampling offset, the interpolation filter index for the Q samples willbe offset from that of the I samples by 4. The coefficients used in theinterpolation filter can alternate between I coefficients and Qcoefficients by switching the address of the RAM 2558 which stores thecoefficients. The interpolation filter indices are represented by theaddress counters 2560 for the coefficients. The address counters 2560for the I and Q coefficients decrease by one when the DF signal 2538goes high for one clock cycle. The output of the interpolation filter2560 is I/Q interleaved.

The interpolated signals are fed to the phase rotation stage 2564, 2566shown in FIG. 25B. There are two multiplier/accumulate elements in thephase rotation circuit. One is used to generate Qr=I*sin (angle)+Q*cos(angle) 2568 and the other to generate Ir=I*cos (angle)−Q*sin (angle)2570. Sine and cosine coefficients are stored in RAMs as look-up-tables2572, 2574. There are 16 sets of sine and cosine values. The addressesof the cosine and sine look up tables (LUT) 2572, 2574 are updated atthe same time as the interpolation filter coefficients 2550, 2552, 2554,2556. The phase rotation circuit 2564, 2566 also operates at twice thecenter frequency. Every second operating cycle produces a pair of validIr and Qr data.

For dynamic apodization, the outputs of the phase rotation 2568, 2570are multiplied by a factor which is dynamically changed during receive.Also if the multiplication factor in a channel is set to zero, thechannel does not contribute to the aperture. This way, dynamic apertureupdating is achieved. I and Q samples are interleaved through amultiplexer (MUX) 2572 to a common multiplier, which reduces themultiplier resources required.

Multi-line Beamforming with Interpolation Filters

The use of interpolation filters for beamforming allows multi-linescanning. In multi-line scanning, several receive lines arereconstructed in the same transmit beam, as shown in FIG. 38. Thetransmit beam is typically broadened with a large depth of field tocover the region where the receive lines will be acquired.

Since the adjacent receive scan lines in a multi-line scan have onlysmall changes in the individual delays for each channel, theinterpolation filter delay implementation allows all lines to beprocessed concurrently. This method works with bandwidth sampling, wherethe interpolation filters can be operated at a rate higher than thesample rate, as is shown in the exemplary conceptual implementation ofthe interpolation filter method for an individual channel in FIG. 39.

In FIG. 39, the digital samples from an individual receive channel's A/Dconverter are sent through a variable length shift register 3902 toimplement a coarse delay of an integer number of samples. The output ofthe variable length shift register 3902 is then sent to a second shiftregister 3904, where the individual shift stages can be accessed. Whenthis second shift register 3904 is filled, the interpolation filter canoperate on a subset of samples, which for the example shown is eightsamples. The interpolation filter provides the fine delay for 1/16wavelength or better resolution. In the example above, the interpolationfilter provides an interpolated sample between cells 4 and 5 of thefilter shift register.

For 3-1 multi-line scanning, as shown in FIG. 40, the interpolationfilter is operated three times for every sample shift. In the example ofFIG. 40, the filter window is offset from the nominal position by onesample backwards for the first receive line, and one sample forward forthe third receive line. In reality, there may be less than a sampledifference in the delay values for the adjacent lines, requiring thatall lines use the same filter window. The position of the filter windowsfor each line is programmable. In situations where the delay differencesare greater than one sample, the filter shift register can be expandedto allow greater separations between windows. For bandwidth sampling,where there are only one or two samples per wavelength, the filterwindows would often not need to be separated by more than one sampleperiod.

The output of the filter operations, as shown in FIG. 40, is timemultiplexed into a single output stream. This stream is summed with thecontributions from other channels to produce the beamformer output. Notethat for 3-1 multi-line the summation circuitry is capable of operatingat three times the sample rate. The summation output of the beamformercan then be de-multiplexed to generate the three multi-line receivelines for downstream processing. The downstream processing is capable ofprocessing three lines in the acquisition time of a single ray line.

In the exemplary receive beamforming methods described above, the outputis a digital data stream of samples representing the sampled RF dataalong a reconstruction line. This stream is derived by summing the datasamples from all receive channels that participate in the receive activeaperture. The RF data stream can be captured in a buffer with sufficientstorage to hold an entire ray line. This same buffer can be used forsynthetic aperture acquisitions, and can be summed with the RF data fromthe second half of the receive aperture as it exits from the summationcircuitry.

For Nyquist or bandwidth sampling schemes with no down-conversion, thesummed RF data stream exits the beamformer as a raw RF stream. This datastream can be converted to a different format using a pair ofcomplimentary 90 degree phase difference filters, often referred to asHilbert transform filters. These filters effectivelyband-pass the RFsignal and down-convert it at the same time to baseband quadrature datastreams. These baseband I and Q data streams can then be combined toprovide echo amplitude data for 2D imaging, or processed further forDoppler blood flow detection. The Hilbert transform filters can also beused to selectively filter and process a portion of the received signalspectrum, as is needed for harmonic imaging, or frequency compounding.In the case of frequency compounding, the filters can be timemultiplexed to produce interleaved output samples from differentfrequency bands of the spectrum.

Referring back again to FIG. 31, the beamformer module 3102 can alsocomprise a beamformer control. To orchestrate the events to form acomplete image frame, the beamformer uses some sort of controller. Thecontroller can be implemented as a simple state machine, which specifiesa series of beamformer events. Each beamformer event can specify atransmit action, a receive action, and/or a signal processing action.Transmit actions specify all the parameters associated with transmittingpulses from the array. These include the duration of connection of thepulsers to the desired elements in the array, the delay times of eachpulser, the transmit waveform characteristics, and the transmit apertureapodization function. Receive actions specify all parameters associatedwith receiving and beamforming the returning echoes. These includespecification of the elements connected to the receive channels, the TGCwaveform to be used for each channel, the A/D converter sample rates,and the dynamic aperture, steering and/or dynamic focus patterns to beused in the reconstruction process. Finally, the signal processingactions specify what to do with the summation output, such as bufferingit for synthetic aperture or sending it to the Hilbert transformfilters. The Hilbert transform filters are specified to perform whateveraction is needed for the beamformer event.

As is apparent from the above description, the control of thebeamforming process can be complex, and a method of handling thiscomplexity is to encode all the information prior to real-time scanningin memory blocks used to control the hardware. The beamformercontroller's task is then reduced to ‘pointing’ to the appropriateportion of the memory block to retrieve the information needed for abeamformer event. Setting up the beamformer for a specific mode ofoperation is then accomplished by loading all the memory blocks withparameter information, then programming the various beamformer eventswith their respective pointers into the controller's state machine. Toperform the scanning mode, the controller is then told to run, and stepsthrough the events for an entire frame of acquisition data. At the endof the frame, the controller looks for a stop signal, and if none isfound, repeats the whole sequence again.

Embodiments of the exemplary ultrasound system are capable of very highacquisition frame rates in some modes of operation, in the range ofseveral hundred frames per second or higher. Just as with otherembodiments according to the present invention , exemplary embodimentsprocess displayed ultrasound image information at 30 fps or lower, evenif the acquisition rates are much higher through the use of asynchronousprocessing as described in reference to FIG. 28. It is to beappreciated, however, that for Nyquist sampled data, the storage isincreased by 50-100%.

Also as previously described, the signal processing hardware/softwarehas random access to the RF memory buffer, and accesses the RF data froma single acquisition frame to produce the displayed estimate data. Inthis exemplary embodiment, the maximum frame rate for signal processingand display is 30 fps, which is typically set by a timer, which signalsthe signal processing task every 1/30^(th) of a second. When processingof a new display frame is complete, the signal processing/display taskwaits for the next 1/30 of a second time tick. At that time, the signalprocessing task reads the ‘Last Frame’ pointer from the Write Controllerto see if a new frame is available. If the ‘Last Frame’ pointer has notadvanced from the previously processed frame, signal processing doesnothing, and waits for the next 1/30 of a second tick. If the ‘LastFrame’ pointer has changed, signal processing begins on the frameindicated by the pointer. In this manner, signal processing alwaysstarts on a 1/30 second tick, and always works on the most recent frameacquired. If acquisition is running much faster than 30 fps, then the‘Last Frame’ pointer will advance several frames with each signalprocessing action.

After the system has been put in freeze, the RF frames stored in thememory buffer can be processed at any desired rate, up to the originalacquisition rate. One simply calculates how many RF frames to advance in1/30^(th) of a second, which is computed as a floating point value thatcan vary from a fraction less than one to as many frames as occurred in1/30^(th) of a second during real time acquisition. With each 1/30^(th)of second tick, signal processing accumulates the frame advance value,until an integer boundary, is crossed. At that time, signal processingprocesses the frame which is that integer boundary number of framesahead of the last frame it processed.

Synthetic aperture beamforming is also supported by this memory bufferscheme. In this case, the various lines which make up the syntheticaperture are acquired into the memory buffer sequentially, so that thesize of an RF storage frame increases. This is simply a differentparameter for the Write Controller, which keeps track of how many linesare written per acquisition frame. For readout, signal processing thencombines the multiple RF lines in a synthetic aperture to produce thefinal result.

The RF data for cineloop playback also provides for re-processing thedata in different ways, bringing out new information. For example, thewall filters for color flow imaging can be changed during playback,allowing optimization for the specific flow conditions. Second, for theresearcher who wants to work with RF data, the buffer memory can dumpedto an external storage device, providing multiple frames of RF data toanalysis. Finally, as a diagnostic tool, the buffer memory can be loadedwith test RF data from the CPU, allowing debug, analysis andverification of the signal processing methods.

For the Nyquist sampled beamforming method, down-converted quadraturesampled data is derived from the RF data for amplitude detection andDoppler processing. This can be obtained with complimentary phase FIRfilters that are designed to have a 90 degree phase difference over thefrequencies in the pass band. These filters can also down-convert thesample stream to a lower sample rate, provided the output sample rate isstill sufficient to sample the range of frequencies in the signal. Toprovide down-converted output samples, the filters operate on RF datathat is shifted by an integral number of cycles of the center frequencyof the spectrum. Alternately, different filters can be designed fornon-integer number of cycle shifts to obtain smaller decimation ratios.A schematic design of an exemplary Hilbert filter, as are known in theart by one of ordinary skill, is shown in FIG. 41.

The filters are designed by first computing a low pass filter designedusing a windowing method. The filter length should be around 40 taps toinsure a good response over a broad range of frequencies, and should bea multiple of the number of samples in the period of the centerfrequency of the RF data. For example, if the sample rate is 120 MHz andthe center frequency is 30 MHz, there are 4 samples in the period of thecenter frequency and an appropriate filter length would be 40 taps (10periods). The low pass coefficients are then multiplied by a sine andcosine function, whose frequency matches the center frequency. In the 30MHz example, each period of the sine and cosine function has 4 samples.

To obtain down-converted samples, the filters are applied on samplesthat are shifted by an integral number of cycles of the centerfrequency. In the 30 MHz center frequency case (sampled at 120 MHz), theRF samples are shifted by 4 samples at a time, leading to a decimationratio of 4 to 1. With this decimation ratio, the input signal isrestricted to 100% bandwidth, otherwise, aliasing of the output sampleswill result.

To obtain smaller decimation ratios, the filters can use alternatecoefficient sets to preserve the phase information. In the 30 MHzexample, to achieve a decimation ration of 4 to 2, two sets ofcoefficients are used—one for 0 degrees phase, and another for 180degrees phase.

These alternate coefficient sets are obtained by sampling the sine andcosine at the appropriate phase increments before multiplying with thelow pass filter coefficients. In this case where the shift betweenoutput samplers is ½ the period of the center frequency, a simple methodto provide the decimation rate is to leave the coefficients the same,and invert the sign of the filter output for the ½ period increments.

The pass band characteristics of the filters can be modified usingdifferent windowing functions. This may be desirable in applicationssuch as harmonic imaging or tracking filters.

Frequency compound can be achieved without additional filters for highdecimation ratios, provided that the filters can operate at the inputsample rate. For the 30 MHz example, two filters can be used withdifferent center frequencies that operate on RF data at two sample shiftincrements. The filter block output a different filter result every twosamples. The two interleaved I,Q samples from the different filters arethen detected and summed together to produce a 4 to 1 decimated detectedoutput.

Example 3

An embodiment of the exemplary system interface to an array with up to256 elements may be used to obtain ultrasound images. Table 4 showsexemplary depth range, field of view, frame rate in B-Mode and framerate in color flow imaging (CFI) for acquiring images. These operatingparameters can be used for the particular small animal imagingapplication described in the far left column. As would be clear to oneskilled in the art, however, other combinations of operating parameterscan be used to image other anatomic structures or portions thereof, ofboth small animal and human subjects.

A small animal subject is used and the animal is anesthetized and placedon a heated small animal platform. ECG electrodes are positioned on theanimal to record the ECG waveform. A temperature probe is positioned onthe animal to record temperature. The important physiological parametersof the animal are thereby monitored during imaging. The anesthetic usedmay be a for example isoflourane gas or another suitable anesthetic. Theregion to be imaged is shaved to remove fuir. Prior to imaging, anultrasound conducting gel is placed over the region to be imaged. Theultrasound array is placed in contact with the gel, such that the scanplane of the array is aligned with the region of interest. Imaging canbe conducted “free hand” or by mounting the array onto a fixture to holdit steady.

B-Mode frame rates are estimated for the different fields of viewindicated in Table 4. Higher frame rates are achievable with reducedfield of view. Color flow imaging (CFI) frame rates are estimated forthe indicated color box widths, with line density one-half that ofB-mode, and with the B-mode image acquired concurrently. TABLE 4Exemplary Depth Range, Field Of View, Frame Rate In B-Mode And FrameRate In Color Flow Imaging (CFI) For Acquiring Images B-Mode Field ColorBox Frame Rate- Frame Rate Depth range of View width B-mode CFI Mousecardiology 3-10 mm  12 mm 8 At least 180 fps At least 60 fps 30 MHzcenter frequency Mouse abdominal 2-12 mm 19.2 mm 12.8 At least 100 fpsAt least 30 fps 30 MHz Mouse, shallow regions,  1-6 mm 12.8 mm 8 Atleast 190 fps At least 80 fps Peripheral Vascular 40-50 MHz Ratcardiology 5-20 mm  24 mm 20 At least 70 fps At least 25 fps 20 MHzcenter frequency

Unaliased velocities measurable with a 150 KHz PRF, for various centerfrequencies and angles are shown in Table 5 for Pulsed Wave (PW)Doppler. TABLE 5 Unaliased Velocities Measurable With 150 KHz PRF, forVarious Center Frequencies and Angles Maximum Maximum Maximum UnaliasedUnaliased Unaliased Center Velocity, Velocity, Velocity, frequency 0°angle 30° angle 60° angle 20 MHz 2.89 m/s 3.34 m/s 5.77 m/s 30 MHz 1.93m/s 2.22 m/s 3.85 m/s 40 MHz 1.44 m/s 1.66 m/s 2.89 m/s 50 MHz 1.16 m/s1.33 m/s 2.31 m/s

A mouse heart rate may be as high as 500 beats per minute, or about 8beats per second. As the number of frames acquired per cardiac cycleincreases, the motion of the heart throughout the cardiac cycle can bemore accurately assessed. The frame rate should be at least 10 framesper cardiac cycle, and preferably 20 for better temporal resolution.Therefore, in one embodiment frames are acquired at a rate of at least160 frames per second, with a field of view large enough to include along axis view of the mouse heart and surrounding tissue (10-12 mm). Forexample, using a 30 MHz linear array, the frame rate for a 12 mm fieldof view is about 180 frames per second. For smaller fields of view, theframe rates used are higher; (e.g., for a 2 mm field of view, with the30 MHz linear array frame rates of over 900 frames per second can beused for viewing rapidly moving structures such as a heart valve).

The maximum velocities present in the mouse circulatory system (in theaorta) maybe as high as 1 m/s in normal adult mice, but in pathologicalcases can be as high as 4-5 m/s. To acquire and display unaliased PWDoppler signals from the mouse aorta, the Pulse Repetition Frequency(PRF) for PW Doppler must be relatively high. In the exemplary system,PW Doppler mode PRFs as high as 150 KHz are used, which for a centerfrequency of 30 MHz and a Doppler angle of 60°, allows for unaliasedmeasurement of blood velocities of 3.8 m/s.

The frame rate for B-Mode Imaging is determined by the two-way transittime of ultrasound to the maximum depth in tissue from which signals aredetected, the number of lines per frame, the number of transmit focalzones, the number of lines processed for each transmit pulse and theoverhead processing time between lines and frames. Images obtained withdifferent transmit focal zone locations can be “stitched” together forimproved resolution throughout the image at the expense of frame rate,which will decrease by a factor equal to the number of zones. Selectionof lower or higher transmit center frequencies for increasedpenetration, or increased resolution, either user selectable orautomatically linked to transmit focal zone location. Multi-lineprocessing, which involves the parallel processing of ultrasound lines,can be used to increase frame rate.

PW Doppler features include a PRF range from about 500 Hz to about 150KHz, alternate transmit frequency selection, the selection of range gatesize and position, the selection of high-pass filter cut-off, and duplexmode operation in which a real-time B-Mode image is displayedsimultaneously with the PW Doppler mode may be the same as the transmitfrequency used in B-Mode, or it may be different. The ability to steerthe PW Doppler beam is dependent on the frequency and pitch of the arrayused, and the directivity of the elements in the array, as would beappreciated by one skilled in the art. For an array with a pitch of 75microns and operating in PW Doppler mode at a transmit frequency of 24MHz, the beam may be steered up to approximately 20°. For this array,larger steering angles would result in unacceptably large grating lobes,which would contribute to the detection of artifactual signals.

Color flow imaging (CFI) can be used to provide estimates of the meanvelocity of flow within a region of tissue. The region over which theCFI data is processed is called a “color box.” B-Mode data is usuallyacquired nearly simultaneously with the Color Flow data, by interleavingthe B-Mode lines with Color Flow lines. The Color Flow data can bedisplayed as an overlay on the B-Mode frame such that the two data setsare aligned spatially. CFI includes a PRF range from about 500 Hz toabout 25 to 75 KHz, depending on the type of array. With 40 MHz centerfrequency and 0° angle between ultrasound beam axis and velocity vector,maximum unaliased velocity will be about 0.72 m/s. Beam steering candepend on the characteristics of the array, (specifically the elementspacing), the transmit frequency, and the capabilities of thebeamnformer; e.g., steering may not be available at the primary centerfrequency, but may be available at an alternate (lower) frequency. Foran array with a pitch of 75 microns and operating in CFI mode at atransmit frequency of 24 MHz, the beam can be steered up toapproximately 20°. Larger steering angles would result in unacceptablegrating lobe levels. Color flow imaging features can include theselection of the color box size and position, transmit focal depthselection, alternate frequency selection, range gate size selection, andselection of high pass filter cut-off. Power Doppler is a variation ofCFI which can be used to provide estimates of the power of the Dopplersignal arising from the tissue within the color box. Tissue Doppler modeis a variation of CFI in which mean velocity estimates from movingtissue are provided. Multi-line processing is a method which may beapplied to the CFI modes, in which more than one line of receive data isprocessed for each transmit pulse transmitted.

The beamformer may be capable of supporting modes in which 2-D imagingand Doppler modes are active nearly simultaneously, by interleaving theB-Mode lines with the Doppler lines. 3-D imaging, as known to one ofordinary skill in the art, utilizes mechanical scanning in elevationdirection.

Throughout this application, various publications are referenced. Thedisclosures of these publications in their entireties are herebyincorporated by reference into this application in order to more fullydescribe the state of the art to which this invention pertains.

Unless otherwise expressly stated, it is in no way intended that anymethod set forth herein be construed as requiring that its steps beperformed in a specific order. Accordingly, where a method claim doesnot actually recite an order to be followed by its steps or it is nototherwise specifically stated in the claims or descriptions that thesteps are to be limited to a specific order, it is no way intended thatan order be inferred, in any respect. This holds for any possiblenon-express basis for interpretation, including: matters of logic withrespect to arrangement of steps or operational flow; plain meaningderived from grammatical organization or punctuation; and the number ortype of embodiments described in the specification.

It will be apparent to those skilled in the art that variousmodifications and variations can be made in the present inventionwithout departing from the scope or spirit of the invention. Otherembodiments of the invention will be apparent to those skilled in theart from consideration of the specification and practice of theinvention disclosed herein. It is intended that the specification andexamples be considered as exemplary only, with a true scope and spiritof the invention being indicated by the following claims.

1. An ultrasound imaging system, comprising: an arrayed ultrasonictransducer having a plurality of elements for transmitting into asubject a transmitted ultrasound signal at a transmitted centerfrequency of up to at least 55 megahertz (MHz); a signal processing unitoperatively connected with said arrayed ultrasonic transducer, whereinsaid signal processing unit is further comprised of, a digital transmitbeamformer subsystem comprised of one or more field programmable gatearrays (FPGA) each having an FPGA clock frequency (FPGA fc) and saiddigital transmit beamformer subsystem having a delay resolution time ofat least [1/(2×FPGA fc)] or greater, a receive beamformer subsystem, afront end electronics module, a beamformer control module, a signalprocessing module, and a computer unit; wherein said signal processingunit is adapted for acquiring a received ultrasound signal having afrequency of at least 15 MHz from said arrayed ultrasound transducerhaving a plurality of elements.
 2. The ultrasound imaging system ofclaim 1, wherein said digital transmit beamformer subsystem furthercomprises a parallel to serial converter having a double data rate (DDR)output, wherein said digital transmit beamformer subsystem is configuredto transmit an ultrasound signal having a transmit center frequency upto at least 55 MHz with a delay resolution time of at least [1/(2×FPGAfc)] or greater by encoding a fine delay and half-cycle sections of saidtransmitted ultrasound signal into up bit words that are converted to aserial bit stream by said parallel to serial converter.
 3. Theultrasound imaging system of claim 2, wherein said digital transmitbeamformer subsystem is configured to transmit an ultrasound signalhaving a transmit center frequency up to at least 55MHz with a delayresolution time of at least [1/(2×FPGA fc)] or greater by encoding afine delay and half-cycle sections of said transmitted ultrasound signalinto up 16 bit words that are converted to a serial bit stream by saidparallel to serial converter.
 4. The ultrasound imaging system of claim2, wherein the transmitted ultrasound signal is comprised of a positivetransmit pulse having a positive pulse width and a negative transmitpulse having a negative pulse width, and said positive pulse width andsaid negative pulse width are independently adjustable.
 5. Theultrasound imaging system of claim 4, wherein said transmittedultrasound signal is comprised of a plurality of positive half-wavecycle sections and each positive half-wave cycle section is comprised ofat least one said positive transmit pulse and said transmittedultrasound signal is further comprised of a plurality of negativehalf-wave cycle sections and each negative half-wave cycle section iscomprised of at least one said negative transmit pulse, and eachpositive transmit pulse is adjustable in duration for each positivehalf-wave cycle section and each negative transmit pulse is adjustablein duration for each negative half-wave cycle section.
 6. The ultrasoundimaging system of claim 5, wherein each fine delay of said at least onesaid positive transmit pulse within each positive half-wave cycle isadjustable and each fine delay of said at least one said negativetransmit pulse within each negative half-wave cycle is adjustable. 7.The ultrasound imaging system of claim 4, wherein the transmittedultrasound signal is comprised of a number of cycles transmitted, andsaid number of cycles transmitted is adjustable.
 8. The ultrasoundimaging system of claim 1, wherein said front end electronics module isconstructed as a replaceable plug-in module.
 9. The ultrasound imagingsystem of claim 1, wherein the signal processing unit is adapted foracquiring the received ultrasound signal from the arrayed ultrasonictransducer and said arrayed ultrasonic transducer is selected from thegroup consisting of a linear array transducer, a phased arraytransducer, a two-dimensional (2-D) array transducer, and a curved arraytransducer.
 10. The ultrasound imaging system of claim 1, wherein thetransmitted ultrasound signal has a transmitted center frequency ofabout 15 MHz up to at least 55 MHz.
 11. The ultrasound imaging system ofclaim 1, wherein the transmitted ultrasound signal has a transmittedcenter frequency of about 15 MHz up to about 55 MHz.
 12. A signalprocessing unit for an arrayed ultrasound imaging system comprising: adigital transmit beamformer subsystem configured to operate up to atleast a 55 MHz transmit center frequency, wherein said digital transmitbeamformer subsystem is further comprised of one or more fieldprogrammable gate arrays (FPGA) and each having an FPGA clock frequency(FPGA fc) and said digital transmit beamformer subsystem having a delayresolution time of at least [1/(2×FPGA fc)] or greater; a digitalreceive beamformer subsystem; a front end electronics module; abeamformer control module; a signal processing module; and a computerunit, wherein said signal processing unit is configured to acquire areceived ultrasound signal from an arrayed ultrasound transducer havinga plurality of elements.
 13. The signal processing unit of claim 12,wherein said digital transmit beamformer subsystem further comprises aparallel to serial converter having a double data rate (DDR) output,wherein said digital transmit beamformer subsystem is configured totransmit an ultrasound signal having a transmit center frequency up toat least 55 MHz with a delay resolution time of at least [1/(2×FPGA fc)]or greater by encoding a fine delay and half-cycle sections of saidtransmitted ultrasound signal into bit words that are converted to aserial bit stream by said parallel to serial converter.
 14. The signalprocessing unit of claim 13, wherein said digital transmit beamformersubsystem is configured to transmit an ultrasound signal having atransmit center frequency up to at least 55 MHz with a delay resolutiontime of at least [1/(2×FPGA fc)] or greater by encoding a fine delay andhalf-cycle sections of said transmitted ultrasound signal into up 16 bitwords that are converted to a serial bit stream by said parallel toserial converter.
 15. The signal processing unit of claim 13, whereinthe transmitted ultrasound signal is comprised of a positive transmitpulse width and a negative transmit pulse width, and said transmit pulsewidth and negative transmit pulse width are independently adjustable.16. The signal processing unit of claim 15, wherein the transmittedultrasound signal is comprised of a number of cycles transmitted, andsaid number of cycles transmitted is adjustable.
 17. The signalprocessing unit of claim 12, wherein said front end electronics moduleis constructed as a replaceable plug-in module.
 18. The signalprocessing unit of claim 12, wherein the signal processing unit isadapted for acquiring the received ultrasound signal from the arrayedultrasonic transducer and said arrayed ultrasonic transducer is selectedfrom the group consisting of a linear array transducer, a phased arraytransducer, a two-dimensional (2-D) array transducer, and a curved arraytransducer.
 19. The signal processing unit of claim 12, wherein thetransmitted center frequency is about 15 MHz up to at least 55 MHz. 20.The signal processing unit of claim 12, wherein the transmitted centerfrequency is about 15 MHz up to about 55 MHz.
 21. A digital transmitbeamformer for an arrayed ultrasound imaging system comprising: one ormore FPGAs each having an FPGA clock frequency (FPGA fc); and a parallelto serial converter having a double data rate (DDR) output, wherein saiddigital transmit beamformer is configured to transmit an ultrasoundsignal having a transmit center frequency up to at least 55 MHz with adelay resolution time of at least [1/(2×FPGA fc)] or greater by encodinga fine delay and half-cycle sections of said transmitted ultrasoundsignal into bit words that are converted to a serial bit stream by saidparallel to serial converter.
 22. The digital transmit beamformer ofclaim 21, wherein the transmitted ultrasound signal is comprised of apositive transmit pulse width and a negative transmit pulse width, andsaid transmit pulse width and negative transmit pulse width areindependently adjustable.
 23. The digital transmit beamformer of claim22, wherein the transmitted ultrasound signal is comprised of a numberof cycles transmitted, and said number of cycles transmitted isadjustable.
 24. The digital transmit beamformer of claim 21, wherein thedigital transmit beamformer is configured to be operatively connectedwith an arrayed ultrasonic transducer and said arrayed ultrasonictransducer is selected from the group consisting of a linear arraytransducer, a phased array transducer, a two-dimensional (2-D) arraytransducer, and a curved array transducer.
 25. The digital transmitbeamformer of claim 21, wherein the transmitted center frequency isabout 15 MHz up to at least 55 MHz.
 26. The digital transmit beamformerof claim 21, wherein the transmitted center frequency is about 15 MHz upto about 55 MHz.
 27. The digital transmit beamformer of claim 21,wherein said digital transmit beamformer is configured to transmit anultrasound signal having a transmit center frequency up to at least 55MHz with a delay resolution time of at least [1/(2×FPGA fc)] or greaterby encoding a fine delay and half-cycle sections of said transmittedultrasound signal into up 16 bit words that are converted to a serialbit stream by said parallel to serial converter.
 28. An ultrasoundimaging system, comprising: an arrayed ultrasonic transducer having aplurality of elements for transmitting into a subject a transmittedultrasound signal at a transmitted center frequency of up to at least 55megahertz (MHz); a signal processing unit operatively connected withsaid arrayed ultrasonic transducer, wherein said signal processing unitis further comprised of, a digital transmit beamformer subsystem, areceive beamformer subsystem, a front end electronics module, abeamformer control module, a signal processing module utilizingquadrature sampling and having a receive sampling frequency, and acomputer unit; wherein said signal processing unit is configured so thatsaid receive sampling frequency may be selectively chosen.
 29. Theultrasound imaging system of claim 28, wherein said receive samplingfrequency is chosen at a frequency different from said transmittedcenter frequency.
 30. The ultrasound imaging system of claim 28, whereinsaid receive sampling frequency is chosen at a frequency the same assaid transmitted center frequency.
 31. The ultrasound imaging system ofclaim 28, wherein said digital transmit beamformer subsystem furthercomprises a transmit focal depth such that said receive samplingfrequency is dependent upon said transmit focal depth.
 32. Theultrasound imaging system of claim 30, wherein said receive samplingfrequency decreases as said transmit focal depth increases.
 33. Theultrasound imaging system of claim 28, wherein said digital transmitbeamformer subsystem further comprises a parallel to serial converterhaving a double data rate (DDR) output, wherein said digital transmitbeamformer is configured to transmit an ultrasound signal having atransmit center frequency up to at least 55 MHz with a delay resolutiontime of at least [1/(2×FPGA fc)] or greater by encoding a fine delay andhalf-cycle sections of said transmitted ultrasound signal into bit wordsthat are converted to a serial bit stream by said parallel to serialconverter.
 34. The ultrasound imaging system of claim 33, wherein saiddigital transmit beamformer subsystem is configured to transmit anultrasound signal having a transmit center frequency up to at least 55MHz with a delay resolution time of at least [1/(2×FPGA fc)] or greaterby encoding a fine delay and half-cycle sections of said transmittedultrasound signal into up 16 bit words that are converted to a serialbit stream by said parallel to serial converter.
 35. The ultrasoundimaging system of claim 33, wherein the transmitted ultrasound signal iscomprised of a positive transmit pulse width and a negative transmitpulse width, and said transmit pulse width and negative transmit pulsewidth are independently adjustable.
 36. The ultrasound imaging system ofclaim 35, wherein the transmitted ultrasound signal is comprised of anumber of cycles transmitted, and said number of cycles transmitted isadjustable.
 37. The ultrasound imaging system of claim 28, wherein saidfront end electronics module is constructed as a replaceable plug-inmodule.
 38. The ultrasound imaging system of claim 28, wherein thesignal processing unit is adapted for acquiring the received ultrasoundsignal from the arrayed ultrasonic transducer and said arrayedultrasonic transducer is selected from the group consisting of a lineararray transducer, a phased array transducer, a two-dimensional (2-D)array transducer, and a curved array transducer.
 39. The ultrasoundimaging system of claim 28, wherein the transmitted ultrasound signalhas a transmitted center frequency of about 15 MHz up to at least 55MHz.
 40. The ultrasound imaging system of claim 28, wherein thetransmitted ultrasound signal has a transmitted center frequency ofabout 15 MHz up to about 55 MHz.
 41. An ultrasound imaging system,comprising: an arrayed ultrasonic transducer having a plurality ofelements for transmitting into a subject a transmitted ultrasound signalat a transmitted center frequency of up to at least 55 megahertz (MHz),wherein said arrayed ultrasonic transducer has a field of view of atleast 5.0 millimeters (mm); a signal processing unit operativelyconnected with said arrayed ultrasonic transducer, wherein saidprocessing unit is further comprised of digital transmit and receivebeamformer subsystems, a front end electronics module, a beamformercontrol and signal processing module, and a computer unit, wherein saidsignal processing unit is adapted for acquiring a received ultrasoundsignal from said arrayed ultrasound transducer having a plurality ofelements at a frame rate of at least 20 frames per second (fps), whereinthe received ultrasound signal has a frequency of at least 15 MHz. 42.The system of claim 41, wherein the signal processing unit furtherproduces an ultrasound image from the received ultrasound signal. 43.The system of claim 42, wherein the received ultrasound signal isprocessed by said signal processing unit to generate the ultrasoundimage at a display rate that is slower than the acquisition rate. 44.The system of claim 43, wherein the display rate of the generatedultrasound image is about 100 fps or less.
 45. The system of claim 44,wherein the display rate of the generated ultrasound image is about 30fps or less.
 46. The system of claim 42, wherein the ultrasound image isproduced by said signal processing unit in an ultrasound mode selectedfrom the group consisting of B-mode, M-mode, Doppler mode, RF-mode, and3-D mode.
 47. The system of claim 41, wherein the signal processing unitis adapted for acquiring the received ultrasound signal from the arrayedultrasonic transducer and said arrayed ultrasonic transducer is selectedfrom the group consisting of a linear array transducer, a phased arraytransducer, a two-dimensional (2-D) array transducer, and a curved arraytransducer.
 48. The system of claim 41, wherein the arrayed ultrasonictransducer has a center operating frequency of at least 15 MHz and thearrayed ultrasonic transducer has an element pitch equal to or less than2.0 times the wavelength of sound at the arrayed ultrasonic transducer'stransmitted center frequency.
 49. The system of claim 41, wherein thearrayed ultrasonic transducer has an element pitch equal to or less than1.5 times the wavelength of sound at the arrayed ultrasonic transducer'stransmitted center frequency.
 50. The system of claim 41, wherein thedigital receive beamformer subsystem comprises using at least one FieldProgrammable Gate Array (FPGA) device.
 51. The system of claim 41,wherein the digital transmit beamformer subsystem comprises using atleast one Field Programmable Gate Array (FPGA) device.
 52. The system ofclaim 41, wherein the front end electronics module further comprises atransmit circuit and a receive channel, wherein the transmit circuitcomprises a transmit supply voltage connected through two field-effecttransistors (FETs) to a transformer with a center-tapped winding inwhich the arrayed ultrasonic transducer is operatively connected to afirst end of a secondary winding of the transformer and an input to thereceive channel is connected to a second end of the secondary winding ofthe transformer such that said transmit supply voltage is set tosubstantially zero and said two FETs are turned on when said receivechannel is receiving a signal and said transformer generates a transmitsignal and couples the transmit signal to the arrayed ultrasonictransducer when said transmit circuit is transmitting a signal.
 53. Thesystem of claim 52, wherein the front end electronics module furthercomprises two or more signal samplers for each receive channel.
 54. Thesystem of claim 53, wherein the signal samplers are analog to digitalconverters.
 55. The system of claim 53, wherein the signal samplers usequadrature sampling to sample a received signal.
 56. The system of claim55, wherein the signal samplers comprise sampling clocks shifted 90degrees out of phase.
 57. The system of claim 56, wherein the samplingclocks have a receive clock period approximately equal to the centerfrequency of a received ultrasound signal.
 58. The system of claim 57,wherein a delay resolution of less than the receive clock period is usedto process the acquired signal.
 59. The system of claim 58, wherein thedelay resolution is 1/16 of the receive clock period
 60. The system ofclaim 41, wherein each element of said arrayed ultrasonic transducerhaving a plurality of elements is operatively connected to a receivechannel.
 61. The system of claim 60, wherein the number of elements ofsaid arrayed ultrasonic transducer having a plurality of elements isgreater than the number of receive channels.
 62. The system of claim 60,wherein the arrayed ultrasonic transducer having a plurality of elementscomprises at least 64 elements that are operatively connected to atleast 32 receive channels.
 63. The system of claim 60, wherein thearrayed ultrasonic transducer having a plurality of elements comprises256 elements that are operatively connected to 64 receive channels. 64.The system of claim 60, wherein the arrayed ultrasonic transducer havinga plurality of elements comprises 256 elements that are operativelyconnected to 128 receive channels.
 65. The system of claim 60, whereinthe arrayed ultrasonic transducer having a plurality of elementscomprises 256 elements that are operatively connected to 256 receivechannels.
 66. The system of claim 60, wherein the arrayed ultrasonictransducer having a plurality of elements comprises 256 elements. 67.The system of claim 66, wherein 512 lines of ultrasound are generated,transmitted into the subject and received from the subject for eachframe of the generated ultrasound image.
 68. The system of claim 66,wherein 256 lines of ultrasound are generated, transmitted into thesubject and received from the subject for each frame of the generatedultrasound image.
 69. The system of claim 41, wherein at least two linesof ultrasound are generated, transmitted into the subject and receivedfrom the subject at each element of the array for each frame of thegenerated ultrasound image.
 70. The system of claim 41, wherein one lineof ultrasound is generated, transmitted into the subject and receivedfrom the subject at each element of the array for each frame of thegenerated ultrasound image.
 71. The system of claim 70, wherein thereceived ultrasound signals are acquired at an acquisition rate of atleast 200 frames per second (fps).
 72. The system of claim 41, whereinthe elements of the arrayed ultrasonic transducer having a plurality ofelements are separated by a distance equal to the wavelength of thecenter transmit frequency of the transducer.
 73. The system of claim 72,wherein the center transmit frequency is selected from the groupconsisting of 15 MHz, 20 MHz, 30 MHz, 40 MHz, 50 MHz, and 55 MHz. 74.The system of claim 41, wherein a length of the arrayed ultrasonictransducer having a plurality of elements is equal to a field of view ofthe transducer.
 75. The system of claim 41, wherein the arrayedultrasonic transducer having a plurality of elements can transmitultrasound into the subject at a center frequency within the range ofabout 15 MHz to about 80 MHz.
 76. The system of claim 41, wherein thereceived ultrasound signal is acquired at a frame rate of at least 200fps.
 77. The system of claim 41, wherein the received ultrasound signalis acquired at a frame rate within the range of about 100 fps to about200 fps.
 78. The system of claim 41, wherein the ultrasound image has alateral resolution of about 150 microns (μm) or less.
 79. The system ofclaim 78, wherein the ultrasound image has a axial resolution of about75 microns (em) or less.
 80. The system of claim 79, wherein theultrasound image has a spatial resolution of about 30 microns (μm) orless.
 81. The system of claim 41, wherein the transmitted ultrasoundsignal can be focused at a depth of about 1.0 mm to about 30.0 mm. 82.The system of claim 81, wherein the transmitted ultrasound signal can befocused at a depth of about 3.0 mm to about 10.0 mm.
 83. The system ofclaim 81, wherein the transmitted ultrasound signal can be focused at adepth of about 2.0 mm to about 12.0 mm.
 84. The system of claim 81,wherein the transmitted ultrasound signal can be focused at a depth ofabout 1.0 mm to about 6.0 mm.
 85. The system of claim 81, wherein thetransmitted ultrasound signal can be focused at a depth of about 3.0 mmto about 8.0 mm.
 86. The system of claim 81, wherein the transmittedultrasound signal can be focused at a depth of about 5.0 mm to about18.0 mm.
 87. A system for producing an ultrasound image, comprising: anarrayed ultrasound transducer having a plurality of elements forgenerating and transmitting into a subject ultrasound at a centeroperating frequency of up to at least 55 megahertz (MHz) and forreceiving ultrasound signals from the subject; and a processing unit forgenerating an ultrasound image frame, wherein each element of thearrayed ultrasound transducer can transmit two or more lines ofultrasound into the subject and receive from the subject two or morelines of echoed ultrasound for each frame of the generated ultrasoundimage.
 88. The system of claim 87, wherein the arrayed ultrasoundtransducer is selected from the group consisting of a linear arraytransducer, a phased array transducer, a two-dimensional (2-D) arraytransducer, and a curved array transducer.
 89. The system of claim 87,wherein the arrayed ultrasound transducer's center operating frequencyis at least 15 MHz and the arrayed ultrasound transducer has an elementpitch equal to or less than two times the wavelength of sound at thearrayed ultrasound transducer's transmitted center frequency.
 90. Asystem for producing an ultrasound image, comprising: an arrayedultrasound transducer having a plurality of elements for generating andtransmitting into a subject ultrasound at a frequency of up to at least55 megahertz (MHz) and for receiving ultrasound signals from thesubject, each element being operatively connected to a receive channel;and a processing unit for acquiring the received ultrasound signals andfor producing an ultrasound image from the acquired signals, wherein theprocessing unit comprises a plurality of signal samplers that usequadrature sampling for acquiring the signals.
 91. The system of claim90, wherein the ultrasound image is produced in an ultrasound modeselected from the group consisting of B-mode, M-mode, Doppler mode,RF-mode, and 3-D mode.
 92. The system of claim 90, wherein the arrayedultrasound transducer is selected from the group consisting of a lineararray transducer, a phased array transducer, a two-dimensional (2-D)array transducer, and a curved array transducer.
 93. The system of claim90, wherein the arrayed ultrasound transducer has a center operatingfrequency of at least 20 MHz and the arrayed ultrasound transducer hasan element pitch equal to or less than two times the wavelength of soundat the arrayed ultrasound transducer's transmitted center frequency. 94.The system of claim 90, wherein each element of the arrayed ultrasoundtransducer is operatively connected to a receive channel.
 95. The systemof claim 94, wherein the number of elements of the arrayed ultrasoundtransducer is greater than the number of receive channels.
 96. Thesystem of claim 94, wherein the processing unit comprises two or moresignal samplers for each receive channel.
 97. The system of claim 96,wherein the signal samplers are analog to digital converters.
 98. Thesystem of claim 97, wherein the signal samplers comprise sampling clocksshifted 90 degrees out of phase.
 99. The system of claim 98, wherein thesampling clocks have a receive clock period approximately equal to thecenter frequency of a received ultrasound signal.
 100. The system ofclaim 99, wherein a delay resolution of less than the receive clockperiod is used to process the acquired signal.
 101. The system of claim100, wherein the delay resolution is 1/16 of the receive clock period.102. The system of claim 90, wherein an acquired signal is processedusing an interpolation filtration method.
 103. The system of claim 90,wherein the processing unit comprises a receive beamformer, wherein thereceive beamformer is implemented using at least one Field ProgrammableGate Array (FPGA) device.
 104. The system of claim 90, wherein theprocessing unit comprises a transmit beamformer, wherein the transmitbeamformer is implemented using at least one Field Programmable GateArray (FPGA) device.
 105. A system for producing an ultrasound image,comprising: an arrayed ultrasound transducer having a plurality ofelements for generating and transmitting into a subject ultrasound at afrequency of up to at least 55 megahertz (MHz) and at a pulse repetitionfrequency (PRF) of at least 500 hertz (Hz), and for receiving ultrasoundfrom the subject, the arrayed ultrasound transducer having a field ofview of at least 5.0 millimeters (mm); and a processing unit forgenerating a color flow Doppler ultrasound image from the receivedultrasound.
 106. The system of claim 105, wherein the arrayed ultrasoundtransducer is selected from the group consisting of a linear arraytransducer, a phased array transducer, a two-dimensional (2-D) arraytransducer, and a curved array transducer.
 107. The system of claim 105,wherein the arrayed ultrasound transducer has a center operatingfrequency of at least 20 MHz and the arrayed ultrasound transducer hasan element pitch equal to or less than two times the wavelength of soundat the arrayed ultrasound transducer's transmitted center frequency.108. The system of claim 105, wherein the PRF is between about 500 Hz toabout 75 KHz.
 109. A system for producing an ultrasound image,comprising: an arrayed ultrasound transducer having a plurality ofelements for generating and transmitting into a subject ultrasound at afrequency of up to at least 55 megahertz (MHz) and at a pulse repetitionfrequency (PRF) of at least 500 hertz (Hz), and for receiving ultrasoundfrom the subject, the arrayed ultrasound transducer having a field ofview of at least 5.0 millimeters (mm); and a processing unit forgenerating a pulsed wave Doppler ultrasound image from the receivedultrasound.
 104. The system of claim 109, wherein the arrayed ultrasoundtransducer is selected from the group consisting of a linear arraytransducer, a phased array transducer, a two-dimensional (2-D) arraytransducer, and a curved array transducer.
 105. The system of claim 109,wherein the arrayed ultrasound transducer has a center operatingfrequency of at least 15 MHz and the arrayed ultrasound transducer hasan element pitch equal to or less than two times the wavelength of soundat the arrayed ultrasound transducer's transmitted center frequency.106. The system of claim 109, wherein the PRF is between about 500 Hz toabout 150 KHz.
 113. A system for producing an ultrasound image,comprising: an arrayed ultrasound transducer having a plurality ofelements for generating and transmitting into a subject ultrasound at afrequency of up to at least 15 megahertz (MHz) and for receivingultrasound signals from the subject, the arrayed ultrasound transducerhaving a field of view of at least 2.0 millimeters (mm); a processingunit for acquiring the received ultrasound signals at an acquisitionrate of at least 300 frames per second (fps) and for generating anultrasound image from the acquired signals.
 114. The system of claim113, wherein the arrayed ultrasound transducer is selected from thegroup consisting of a linear array transducer, a phased arraytransducer, a two-dimensional (2-D) array transducer, and a curved arraytransducer.
 115. The system of claim 113, wherein the arrayed ultrasoundtransducer has a center operating frequency of at least 20 MHz and thearrayed ultrasound transducer has an element pitch equal to or less thantwo times the wavelength of sound at the arrayed ultrasound transducer'stransmitted center frequency.
 116. The ultrasound imaging system ofclaim 1, wherein FPGA fc is the highest operable frequency of the one ormore FPGA.
 117. The signal processing unit of claim 12, wherein FPGA fcis the highest operable frequency of the one or more FPGA.
 118. Thedigital; transmit beamformer of claim 21, wherein FPGA fc is the highestoperable frequency of the one or more FPGA.